Key words
vascular - MR-angiography - imaging sequences - AVM - arteries
Introduction
MR angiography strategies have undergone constant refinement since the introduction
of contrast-enhanced MR angiography by Prince et al. in 1993 and dynamic imaging using
the “keyhole” method by van Vaals et al. and Jones et al. that same year. In particular,
parallel imaging had a large impact on increasing the temporal efficiency of data
collection sufficiently dynamically showing the contrast medium bolus passage in the
blood vessel with high spatial resolution [1]
[2]
[3]
[4]
[5]. For the simultaneous imaging of flow dynamics and vascular anatomy, the invasive
method of catheter angiography in the form of digital subtraction angiography (DSA)
is the reference standard against which all new methods have to compete.
Dynamic information about blood flow in vessels is essential for functional analysis
of arterial inflow and venous outflow of vascular malformations, for example. However,
TR-MRA can also be helpful when it is necessary to image multiple vascular territories
simultaneously while administering low doses of contrast medium, e. g. in children
and patients who can tolerate only short examination times [6]
[7]. 4D-MRA is generally useful for every clinical problem involving a short arteriovenous
transit time, for example in the pulmonary artery flow path, where it has ben used
to investigate arteriovenous fistulae and shunts [8]
[9]
[10]
[11]
[12]
[13]. This review provides an overview of the temporal resolution MR angiography techniques
currently used routinely and their development, while presenting various clinical
applications in which these techniques have already been employed successfully. Diagnosing
cerebral arteriovenous malformations (cAVM) is an example of a key clinical application
for comparing individual methods, since these malformations can be examined using
all of the techniques described in the article, and data from prospective studies
have already been published and in turn cited in this article.
The development of temporal resolution MR angiography techniques
The development of temporal resolution MR angiography techniques
The first temporal resolution MR sequences were developed to roughly image the bolus
passage of contrast agents and thereby ascertain bolus arrival time. For this purpose,
T1-weighted gradient echo techniques single-thick slice-(known as 2D-MRA) were created.
At that time, however, significant compromises had to be made in terms of spatial
resolution to facilitate achieving the requisite very short time intervals of 1 – 2
seconds [14]
[15]
[16].
This idea of dynamically tracking a contrast medium bolus (integrated with a mask
subtraction of non-contrast images) is indispensable for planning and facilitating
precise temporal initiation of static sequences such as high spatial resolution volume
data sets (3D-CEMRA), which absolutely require precise “timing”, i. e. a precise starting
time (fluoroscopic triggering).
T1-weighted 2D-multi-slice and 3D-gradient echo sequences are generally suited for
showing the arrival of a contrast medium bolus with a high signal-to-noise ratio.
However, to achieve a high image refresh rate in this process, it is necessary to
limit the k-space portions that are actually scanned. First, image acquisition was
accelerated using above all the symmetry characteristics of the k-space. Major advancements
in the acceleration of dynamic sequences were then achieved through the introduction
of parallel imaging [17]
[18]
[19], the use of higher field strengths with a more favorable signal-to-noise ratio and
the use of complex, strategic k-space acquisition schemes. One such scheme is “echo
sharing”, which is the practice of strategically distributing k-space acquisition
over the sequence duration and using a certain temporal interpolation to reconstruct
k-space. What is critical here is that the portion of k-space (central portion) that
essentially determines image contrast is scanned at a higher frequency than k-space
portions (peripheral portions) that are less significant to image contrast. This allows
contrast change to be mapped over time even if only a small portion of k-space is
actually acquired per dynamic phase [20]
[21]. Through the use of higher field strengths and improved coils [11]
[22]
[23]
[24] sequences were established in the last decade that simultaneously facilitate both
high temporal and spatial resolution in dynamic vascular imaging. The result was a
steady increase in publications on the field of 4D-MRA which continues to this day
([Fig. 1a]). Because the development of these complex techniques required close cooperation
between clinical institutions and commercial partners, the various “echo-sharing”
techniques were used mostly in a manufacturer-specific manner ([Table 1]). These techniques are listed in this review according to method.
Fig. 1 Original publications on time-resolved MRA between 2000 and 2012; a Number of publications related to field strength; b Publications broken down by TR-MRA technique.
Table 1
Time-resolved contrast-enhanced TR-MRA techniques.[1]
|
TR-MRA technique
|
year
|
field strength
|
manufacturer
|
|
keyhole
|
1993
|
1.5 T
|
Philips Healthcare, Best, Netherlands
|
|
4D-TRAK
|
2008
|
1.5 T
|
Philips Healthcare, Best, Netherlands
|
|
2008
|
3.0 T
|
Philips Healthcare, Best, Netherlands
|
|
4D-TRAK+
|
2011
|
3.0 T
|
Philips Healthcare, Best, Netherlands
|
|
TRICKS
|
1996
|
1.5 T
|
General Electric Healthcare, Milwaukee, WI, USA
|
|
PR-TRICKS
|
2002
|
1.5 T
|
General Electric Healthcare, Milwaukee, WI, USA
|
|
HYPR PR-TRICKS
|
2006
|
1.5 T
|
General Electric Healthcare, Milwaukee, WI, USA
|
|
2007
|
3.0 T
|
General Electric Healthcare, Milwaukee, WI, USA
|
|
TREAT
|
2005
|
1.5 T
|
Siemens Healthcare, Erlangen, Deutschland
|
|
2006
|
3.0 T
|
Siemens Healthcare, Erlangen, Deutschland
|
|
TWIST
|
2008
|
1.5 T
|
Siemens Healthcare, Erlangen, Deutschland
|
|
2010
|
3.0 T
|
Siemens Healthcare, Erlangen, Deutschland
|
1 Year = year first described in technical literature; Manufacturer = manufacturer
of the MR systems on which the indicated technique was implemented at the time
As mentioned above, that was used to accelarate dynamic imaging cAVM are especially
well suited for testing the effectiveness of 4D-MRA. This clinical picture was therefore
examined in clinical studies using each of the methods introduced, resulting in data
that facilitates good comparison. The currently employed “echo-sharing” techniques
are introduced below and compared using the example of cAVM imaging in view of the
good body of data:
“Keyhole”-based techniques
“Keyhole”-based techniques
In 1993, the same year contrast-enhanced 3D-CEMRA was introduced by Prince et al.,
Van Vaals et al. and Jones et al. described separate techniques which involved repetitively
scanning the central k-space, while acquiring the peripheral k-space only once. Afterwards,
missing information from the one-time scanning of the peripheral k-space is added
to each of the incomplete, central, dynamic data sets to finally generate complete
k-space data sets for each point in time [2]
[3].
The complete data set from which the missing k-space portions are “borrowed” is identified
as the reference data set and is usually acquired after the dynamic phases upon completion
of the sequence. In only 1993 Van Vaals declared that the “keyhole" technique should
be combined with other acceleration methods “based on different principles” to achieve even higher acceleration.
This predicted development was realized in the subsequent two decades as a result
of different techniques facilitating accelerated data acquisition actually being developed.
“Temporal resolution MR angiography with CENTRA-Keyhole” (4D-TRAK, Philips Healthcare,
Best, Netherlands) represents the combination of multiple acceleration techniques
with keyhole imaging and already enjoys routine clinical use. This technique combines
the keyhole principle with a randomized acquisition of central k-space data (CENTRA-Keyhole),
parallel imaging (SENSE) with high acceleration factors and half-Fourier acquisition
[25]
[26]
[27]. Further refinement of the technique involves subdividing the central k-space partition
(the “keyhole window”) into three smaller fractions, which are likewise acquired alternatingly
(temporal resolution MR angiography with keyhole and view sharing [4D-TRAK+]; [Fig. 2a]) [28].
Fig. 2 K-space acquisition using various 4D-MRA techniques; K-space acquisition schemes
in phase encoded (ky), slice encoded (kz) and frequency encoded direction (kx). A “zero filling” non-acquired k-space regions is not illustrated in graphics a
through d. a Keyhole acquisition with view-sharing (4D-TRAK+): During dynamic imaging phase, either
segment A or one of the segments B and C is scanned on an alternating basis. Area
D is scanned following the dynamic acquisition phase and added to all dynamic acquisitions.
b 3D-TRICKS: Initial concept with four equally sized Ky-segments (containing the same
number of (ky, kz) points) with A, B, C and D. Either segment A or one of the segments B, C and D is
scanned on an alternating basis. Complete k-spaces are yielded by putting together
all temporally neighboring segments A, B, C and D. c TREAT: Concept with n possible regions. The regions A, B, C and D contain the same
number of (ky, kz) points and are divided according to their distance from the center of the k-space
into the innermost segment A and the additional peripherally located segments B, C
and D. Either segment A or one of the segments B, C and D are scanned on an alternating
basis, and complete K-spaces are yielded in turn by putting together the temporally
neighboring segments A, B, C and D. d TWIST: In each dynamic phase the central portion of k-space is scanned, while only
a fraction of the peripheral region B is scanned. This region is comprised of elliptical
trajectories interwoven (“twisted”) with one another. Missing data needed for assembling
a complete k-space are taken from the respective temporally neighboring dynamic phases.
Keyhole techniques were used for examining the abdomen, thorax and extremities as
well as the head and neck at 1.5 T [29]
[30]
[31]
[32]
[33]
[34]
[35]
[36] and the pelvis, thorax and extremities as well as the head and neck at 3.0 T [26]
[28]
[37]
[38]
[39]
[40]
[41]
[42]
[43]
[44]
[45]
[46]
[47].
For example, these techniques allowed the imaging of surgically created shunt connections
between the superior vena cava and the pulmonary artery during Fontan procedures.
This technique was likewise used to image dialysis shunts or to acquire purely arterial
images of the lower leg region in cases of asymmetrical contrast perfusion.
In principle limitations in the complete suppression of the venous signal can appear
with keyhole-based techniques if too small a fraction of the central k-space is selected.
Caution is advised when using very high compression factors with 4D-TRAK+, since a
flickering artefact can appear in cinematic view [28]. This is based on the fact that 100 % symmetrical boundary conditions are never
present in k-space due to noise and that when high compression factors are present
only positive or negative central k-space portions can be used for image reconstruction
on an alternating basis. This results in deviations, albeit minor, in image contrast
(“flickering”). Taking these limitations into account, a temporal resolution of 572 ms
at a simultaneous spatial resolution of (1.1 × 1.1 × 1.1) mm³ was achieved when 4D-TRAK+
was used for examining cAVM, for example, while imaging all cranial blood vessels
[41].
TRICKS
In 1996 Korosec et al. described a technique named 3D-TRICKS (time-resolved imaging
of contrast kinetics) [42] in which different k-space portions are acquired over a period of time, and missing
portions are borrowed from prior or subsequent data sets ([Fig. 2b]) in the sense of a temporal interpolation [43].
The peripheral (higher frequency) portions of k-space (B, C and D) are scanned three
times less frequently than the central (lower frequency) portions (A). Using these
k-space fractions, data collection is repeated according to the following sequence,
for example: D, A, C, A, B, A. In addition, the entire k-space is scanned at the beginning
and end of the TR-MRA sequence with all of its four portions.
Various enhancements to this acquisition scheme were subsequently developed. For example,
(PR)-TRICKS uses radial projection reconstructions on the kxky plane combined with a variable k-space scanning rate for accelerated dynamic data
acquisition [44]. Cartesian coding is then employed in the slice encoding direction. The next step
was “HYPR TRICKS”, which added “highly-constrained back-projection reconstruction“
(HYPR) to improve the dynamic low-frequency data of the TRICKS-algorithm as well as
(by means of high-frequency data) the signal-to-noise ratio and thus both temporal
as well as spatial resolution with the aid of an additional high-resolution data set
following venous filling [45]
[46]. Combining all of these methods (HYPR PR-TRICKS), however, results in high sensitivity
to patient movements, which can in turn compromise image quality [47]. It is therefore necessary to precisely weigh the advantages and disadvantages of
these highly complex acquisition schemes to find the ideal compromise for the particular
clinical application. Applications for the abdomen, thorax, extremities and head and
neck at 1.5 T [48]
[49]
[50]
[51]
[52]
[53]
[54]
[55]
[56]
[57]
[58]
[59]
[60]
[61]
[62]
[63]
[64] and for the head and neck as well as the extremities at 3.0 T [65]
[66]
[67]
[68]
[69]
[70]
[71]
[72] have been published.
Literature contains examples of clinical applications of TRICKS-4D-MRA for pulmonary
angiographies, for diagnosing carotid-cavernous sinus fistulae as well as for improved
diagnosing of diseases in the arteries of the lower legs, particularly in patients
with diabetes mellitus. As with all 4D-MRA techniques, limitations of the TRICKS technique
can appear through temporal interpolation.
In the case of HYPR-TRICKS techniques, low data density (“sparsity”) can result in
signal fluctuations. It was shown that very high image refresh rates can be achieved
with HYPR-TRICKS while employing to some extent very complex reconstruction algorithms
and extremely low portions of actually acquired data. Based on the clinical application
example of examining cAVM, an image refresh rate of 0.8 s at a voxel size of 0.5 × 0.75 × 4mm³
was achieved using a TRICKS algorithm [69].
TREAT
TREAT (time-resolved echo-shared angiography technique) was first described in 2005
by Fink et al. and divides the k-space into n regions (for example, regions A, B,
C and D when n = 4) [73]. Each region covers an equal portion of k-space and thus the same number of (ky, kz) points ([Fig. 2c]).
Following complete k-space acquisition, the scanning of the central segment A and
one of the peripheral segments B, C or D alternates similar to the scheme employed
in the TRICKS technique. To reconstruct the images, complete k-space data is generated
by summarizing the k-space data of the next consecutive acquisitions.
For a segmentation pattern with n segments, a complete data set can then be reconstructed
in intervals of 2 • TA/n (TA being the time needed for obtaining a complete data set).
However, as the number of segments increases, the signal intensity is distributed
further over the image plane, resulting in increasingly less defined smaller blood
vessels.
Numerous studies use this technique on various regions of the body at 1.5 T [12]
[73]
[74]
[75]
[76]
[77]
[78]
[79]
[80]
[81]
[82]
[83] and in the head and neck at 3.0 T [85]
[86]
[87]
[88]. Among the published indications for these examinations are the imaging of pathological
flow conditions with the occurrence of endoleaks in cases of aortic prostheses, [76] as well as diagnosing pulmonary embolisms [83] or subclavian steal syndromes [84]. Possible limitations arise from the fact that each data set is reconstructed from
similarly sized portions of k-space partitions from various points in time and is
thus interpolated over time. This particularly effects the imaging of small blood
vessels to the extent that neighboring small arteries and veins can no longer be distinguished
from one another. Using the TREAT algorithm, a temporal resolution of 1.5 s per 3 D
data set with a simultaneous spatial resolution 1.2 × 1.0 × 4 mm3 was achieved when imaging cAVM [88].
TWIST
The details of the TWIST technique (time-resolved imaging with stochastic trajectories)
were reported by Vogt, Lim and Song over the period of 2007 to 2009 [89]
[90]
[91]. In this technique, all points in the k-space are sorted according to their radial
distance from the center of the k-space. A critical radial distance can be defined
around the k-space and subdivided into two subareas, a central region A (low-frequency
portions) and a peripheral region B (high-frequency portions) ([Fig. 2 d]).
During data acquisition, the data of the entire k-space is gathered only once, either
at the beginning or end of the sequence. For the dynamic phase of image acquisition,
the entire region A within each time window is acquired, while one of n portions is
scanned from region B, and missing data points are taken from temporally adjacent
acquisitions of region B for complete k-space reconstruction.
In this process, the k-space trajectories of region B follow a spiral pattern on the
ky-kz plane, with the trajectories from region B being intertwined with one another, giving
the sequence its name. With TWIST, acceleration is based on both the size of region
A and the density of trajectories in region B. This technique has been used on the
abdomen, thorax, extremities as well as on the head and neck at both 1.5 T [92]
[93]
[94]
[95]
[96] and 3.0 T [92]
[97]
[98]
[99]
[100]
[101]
[102]
[103]
[104]. TWIST has likewise been used to image ovarian vein reflux [92] as well as thoracic venous outflow obstructions [94], examine pathologies of the abdominal aorta [100] and successfully diagnose changes in flow conditions in cases of peripheral occlusive
arterial disease [97]. However, the complex acquisition pattern of TWIST data recording with its data
collection interwoven over the acquisition time poses special challenges for assigning
artefacts to certain k-space portions, which is made even more difficult by the fact
that artefacts are always present in multiple consecutive data sets because of the
temporal interpolation reconstructed of the data. Regardless of these limitations,
patients with cAVM, for example, have been successfully examined at a temporal resolution
of 0.58 s and a voxel size of (1.6 × 1.6 × 1.6)mm3 [103]
Summary and supplemental technical observations
While implementing TR-MRA demands high standards for software and hardware, current
tomography machines from major manufacturers implement high-quality manufacturer-specific
TR-MRA sequences. Each of these techniques has its pros and cons that would make particular
methods appear to be optimal for particular cases.
It must be emphasized that images reconstructed from complex temporally intertwined
data generally do not correspond to any exact visualization of a single time point
(temporal interpolation). However, the central k-space portions used exclusively at
a particular point in time are essential for the image contrast of the corresponding
image so that the contrast curve can be realistically mapped.
Because of the potential cons of this temporal interpolation, Riederer et al. have
introduced the concept of “temporal footprint" of high temporal resolution sequences.
This concept describes the period of time that is needed to acquire a complete k-space
data set, i. e. the entire k-space portions. Dividing the k-space into multiple portions
in the process of time-resolved imaging would produce the following "temporal footprint"
in which the exemplary constellation has 4 equal-sized portions A-D (acquisition duration
1 s each, A = central k-space portion):
Example 1 ([Fig. 3a]): Acquisition in the sequence A, B, C, D...; central k-space portions are acquired
every 4s; the temporal footprint is the product of the summation of individual k-space
portions A-D, with the acquisition time between each being omitted, resulting in a
temporal footprint = 4 s.
Fig. 3 Image refresh rate (contrast refresh) scheme compared to "temporal footprint" in
the case of two different acquisition schemes a, b.
Example 2 ([Fig. 3b]): Acquisition in the sequence A, B, A, C, A, D…; central k-space portions are acquired
alternatingly with peripheral k-space portions B, C or D every 2 s. The temporal footprint
is, in contrast, the product of the summation of individual k-space portions A-D plus
the intermediate acquisition times, resulting in this case in a temporal footprint = 6 s.
In Example 2, contrast information is accordingly refreshed every 2 s, while only
every 4 s in Example 1. However, Example 1 is the temporally “cleaner” representation,
since the temporal footprint is shorter. For TRICKS, TREAT and TWIST the “temporal
footprint” is in each case accordingly a multiple of the time duration of an individual
dynamic phase and reflects the period of time over which the acquisition of a complete
k-space data set extends.
On the other hand, it would not be wise to apply this concept to keyhole-based methods,
since the entire peripheral k-space in this instance is acquired only once, which
would thus yield periods of differing length for the “temporal footprint”, each depending
on what point in time the acquisition of the central k-space is observed [28].
Regardless of the technique employed, a high degree of temporal accuracy in the collected
dynamic data is desired in clinical applications. Future studies are needed to more
accurately examine which technique constitutes the optimal compromise between temporal
interpolation, “temporal footprint” and image for a particular clinical problem [105]
[106].
For precisely imaging smaller structures, in particular, the signal-time-curve (“point
spread function”) is ultimately of special importance. Temporal interpolation can
result in inferior definition that can manifest itself in, for example, limitations
in imaging small arterial supply vessels of arteriovenous malformations [26]
[107]. With increasing segmentation, the inferior definition of the peak of the signal-to-time
curve becomes more pronounced, which also limits the degree of the possible segmentation
steps in the increasingly complex acquisition schemes [73].
Clinical perspectives
The technical methods for acquiring 3D-CEMRA image series, some of which are highly
complex, are already facilitating detailed observation of numerous pathological changes
in flow that were previously the domain of invasive DSA. [Fig. 1b] provides a quantitative overview of which methods have come into use in the past
few years. [Fig. 3], [4], [5], [6] provide several examples of images, while [Table 2] offers an overview of clinical applications to date and shows the multifaceted application
possibilities of 4D-MRA. Established routine clinical applications in the meantime
include the diagnosis of arteriovenous malformations or fistulae. Unlike conventional
static sequences, these applications allow the imaging of premature filling of veins
or sinuses by shunt mechanisms. Pathological flow conditions that would otherwise
be possible to reconstruct only with invasive methods can likewise be shown in cases
of aortic dissections, endoleaks from aortic prostheses or subclavian steal syndrome.
Finally, the method sees frequent routine clinical use in generating purely arterial
images of the lower leg in cases of asymmetrical arterial filling due to upstream
stenoses (in peripheral occlusive arterial disease) or arteriovenous shunts (often
in cases of diabetic microangiopathy). In these cases, precise timing for adjusting
arterial perfusion and thus a pure arterial 3D-CEMRA is oftentimes not possible.
Fig. 4 75-year old patient with stage III peripheral arterial occlusive disease, ambulant
< 50 m, complaints primarily on the right side. Total volume maximum intensity projections
of high temporal resolution 4D-MRA show the lower legs prior to arrival of contrast
agent (a), arterial bolus passage (b–d), and premature venous enhancement in the right lower leg resulting from a shunt
between the right peroneal artery (arrows in d, e) and the great saphenous vein, as well as venous filling in a later phase f.
Fig. 5 69-year old female patient with acute swelling of the left arm presenting septic
clinical picture, imaging performed to exclude thrombosis. Representative total volume
maximum intensity projections per one phase of 4D-MRA prior to arrival of contrast
agent bolus a, during arterial bolus passage b and during venous phase of contrast agent passage c.
Fig. 6 25-year old male patient before a – f and after g – l surgical resection of a right frontal cerebral arteriovenous malformation (arrow
in d) in a non-eloquent area of the brain. Lateral total volume maximum intensity projections
of temporally corresponding phases of contrast-enhanced 4D-MRA.
Table 2
Clinical applications of TR-MRA.
|
bodily region
|
clinical problem
|
references
|
|
head
|
carotids
|
[95]
[114]
[115]
[116]
|
|
cerebral arteriovenous fistulae and malformations
|
[33]
[47]
[65]
[117]
[118]
[119]
|
|
cavernous hemangioma
|
[117]
[120]
|
|
sinus thrombosis
|
[33]
[121]
|
|
multiple sclerosis
|
[122]
[123]
[124]
|
|
orbital lesions
|
[65]
[125]
|
|
spinal column
|
spinal arteries
|
[30]
[71]
[126]
|
|
arteriovenous fistulae and malformations
|
[54]
[72]
[76]
|
|
thorax/abdomen
|
aortic dissection
|
[17]
[127]
|
|
aortic isthmus stenosis
|
[128]
|
|
pulmonary embolisms
|
[63]
|
|
pulmonary perfusion
|
[9]
[10]
[12]
[13]
[29]
|
|
pulmonary hypertension
|
[8]
[11]
|
|
arteriovenous malformations
|
[36]
[129]
|
|
endoleaks from vascular prostheses
|
[82]
[130]
[131]
|
|
subclavian steal syndrome
|
[90]
|
|
coronary vessels
|
[132]
[133]
[134]
|
|
renal artery stenoses
|
[135]
[136]
[137]
|
|
pelvic congestion
|
[32]
[57]
[98]
[138]
[139]
|
|
arteries of the extremities
|
asymmetrical contrast perfusion
|
[56]
[99]
[140]
[141]
[142]
[143]
|
|
arteriovenous malformations
|
[144]
[145]
[146]
|
|
diabetic microangiopathy
|
[31]
[147]
[148]
[149]
[150]
|
That cAVM was examined notably using 4D-MRA techniques [23]
[26]
[61]
[69]
[72]
[103]
[150]
[151]
[152]
[153], can be explained by the fact that on the one hand intracranial vessels are particularly
suited given their fundamentally low susceptibility to artefacts in view of the circumscribed
examination volume without significant patient movements including breathing. On the
other hand, the dynamic information offers especially high potential benefits, and
the reference standard of DSA is frequently on hand for comparative purposes.
TR-MRA, however, also opens numerous new diagnostic avenues. For example it is conceivable
when using an intravascular contrast agent to first acquire detailed functional information
with the aid of TR-MRA (e. g. for diagnosing a pulmonary embolism) and then to image
an underlying leg vein thrombosis with the aid of a high-resolution spatial sequence
[154]
[155]. Primarily intravascularly dwelling contrast agents of this type with reversible
protein binding and thereafter considerably delayed pervasion of the interstitium
are currently available only in North America.
In the studies on clinical applications of TR-MRA some of which involved high image
refresh rates and high spatial resolution, the majority of temporal information was
displayed and at the same time the contrast agent dose administered was oftentimes
significantly reduced compared to the static, high spatial resolution 3D-CEMRA. In
the future, combining echo-sharing techniques with special data reconstruction methods
using only a fraction of the actually required data (HYPR, compressed sensing) may
possibly allow even significantly higher image refresh rates, thereby facilitating
the generation of real-time sequences and detailed examination of flow conditions
[156]
[157].
Disadvantages compared to DSA resulting from the simultaneous contrast agent perfusion
in all vascular segments (a not insignificant advantage of DSA is the possibility
of selective contrast agent administration) are compensated partly with a vascular
selective excitement using what is known as arterial spin labelling (ASL) [34]
[158]. In the future, further insight on flow dynamics may possibly be gained through
techniques such as high temporal and spatial resolution and at the same time quantitative
phase contrast angiography (4D-PC-MRA), which has lately shown considerable promise
[159]
[160]
[161]
[162]
[163]
[164]
[165]. Finally, real-time imaging, for example during catheter interventions with susceptibility
markers, is a promising area of application for 4D-MRA. However, this is the subject
of predominantly preclinical studies [165]
[167].
Summary
TR-MRA was initially used only for facilitating fluoroscopic bolus triggering and
gaining exact timing for performing a high spatial resolution static, pure arterial
3D-CEMRA, for instance, of the supra-aortic arteries. With the aid of complex k-space
acquisition algorithms, parallel imaging and new echo-sharing techniques while at
the same time at higher spatial resolution. This is opening up new areas of application
that had mainly eluded non-invasive testing until now. It will be exciting to see
what benefits further technological advancements in both coil and scanner technology,
such as for example fully digitalized signal transmission and reception, will have
for TR-MRA in the future and what importance this innovative technology will have
in routine clinical use.
