Ultra-High Contrast MRI of the Brain and Spinal Cord using Directly Acquired and Synthetic Bipolar Filter Images

1. Introduction

Ultra-high contrast MRI is a term used to describe MR imaging that shows abnormalities with high contrast when little or no abnormality is seen using conventional state-of-the-art MRI sequences. It is achieved without the use of increased static or gradient magnetic fields. For soft tissues, Xray CT can be regarded as high contrast, conventional state-of-the-art MRI as very high contrast and MRI which shows abnormalities with obvious contrast when they are not seen with conventional MRI as ultra-high contrast (UHC) [1].

A common mechanism for achieving UHC MRI is synergistic contrast in which changes in a single tissue property such as T₁ are used twice or more in the same sequence to increase contrast rather than just once which is the case with most conventional sequences [2]. An example is the divided subtracted inversion recovery (dSIR) sequence in which the signals from two inversion recovery (IR) sequences with different inversion times (TIs) are subtracted to increase the contrast produced by small changes in T₁. This contrast is increased further by division of the subtraction by the sum of the signals from the two sequences [3].

Another way of achieving UHC MRI is to use a high quality single tissue property map such as a T₁ or T₂ map and retrospectively apply a shaped filter to the map. The filter can increase contrast in one or more domains of tissue property values and maintain anatomical detail in the rest of the image. This is unlike narrow windowing of images which, when used to increase contrast, is accompanied by saturation of the display gray scale at the upper and lower signal thresholds. This leads to loss of anatomical detail and limits the degree to which contrast can be increased by windowing.

The principal clinical focus of UHC MRI to date has been on small changes in tissue properties from normal that are insufficient to generate useful contrast with conventional state-of-the-art sequences. If abnormalities that are already seen with high contrast using conventional sequences, there is no particular premium in demonstrating them with even greater contrast.

Small changes in T₁ may produce obvious abnormalities with the dSIR sequence as illustrated in a case of mild traumatic brain injury (mTBI) in an 18-year-old male patient shown in Figure 1. No abnormality is seen on the T₂-FLAIR image in the patient (Figure 1A). The dSIR sequence in a normal age matched control shows normal white matter in the cerebral hemispheres as low signal (dark) (arrows) in Figure 1B. The same dSIR sequence in the patient shows abnormal high signal in his entire white matter (arrows) (Figure 1C). High signal (light) well-defined boundaries are seen between normal white and gray matter on the dSIR image in Figure 1B. These are less obvious in Figure 1C because of the high signal in the abnormal white matter.

High contrast abnormalities in white matter have been seen using dSIR T₁-bipolar filter images of the type illustrated in Figure 1 in areas where little or no abnormality has been seen with T₂-FLAIR or T₂-wSE sequences in cases of mTBI [4], multiple sclerosis (MS) [5], methamphetamine substance use disorder [6] and Grinker’s myelinopathy [7].

The purpose of this educational review is to describe the basic physics underlying UHC MRI using bipolar filter images and illustrate use of these images in patients in order to facilitate wider use of them in clinical practice.

2. Basic Physics

2.1. Tissue Property Filters (TP-filters) and the Inversion Recovery (IR) Sequence

The first part of this paper is a condensed and updated version of work published previously [1,2,3]. It is included to make the paper self-contained and not require concurrent reference to other papers to understand the contrast of clinical images included in the paper. Instead of illustrating image contrast by plotting longitudinal and then transverse magnetisation (M_Z and then M_XY) against time using the Bloch equations as in Figure 2, it is possible to use plots of signals produced by the exponential recovery of longitudinal magnetisation and exponential decay of transverse magnetisation against T₁ and T₂ respectively. These plots are tissue property filters (TP-filters); the tissue properties may be mobile proton density, T₁, T₂, T₂*, D*, etc [8,9]. In this paper the term tissue is used to include fluids unless otherwise specified.

For TR >> T₁, the T₁ dependent part of the IR sequence has the signal equation:

S_T1 = 1-2e^-TI/T₁

(1)

where S_T1 is the signal from the T₁-filter, TI in the inversion time and T₁ is the longitudinal relaxation time. The T₁-filter of the IR sequence (with a constant value of TI) is shown in phase-sensitive or signed form in Figure 3A where it is a monotonic low pass filter, and in magnitude form in Figure 3B where it is a negative unipolar filter. The maximum size of the slopes of these two filters are shown with red lines in Figure 3A,B. The magnitude forms of the IR filter S_T1 = (1-2e^-TI/T₁) for T₁ < $\frac{\mathrm{TI}}{\ln 2}$ and S_T1 = (2e^-TI/T₁ -1) for T₁ > $\frac{\mathrm{TI}}{\ln 2}$ are used in the subsequent text unless otherwise specified.

When TI is increased, the magnitude IR T₁-unipolar filter shifts to the right as shown in Figure 4. Figure 4A (left) shows the IR T₁-filter with a short TI_s (e.g., the Short TI IR or STIR sequence) for brain where gray matter (G) has a higher signal than white matter (W). The slope of the T₁-filter between W and G is moderately positive (red line).

When the TI is increased to an intermediate TI, TI_i, as in Figure 4B (centre), the T₁-filter is shifted to the right. W and G are fixed in the same position on the X axis, and W now has a higher signal than G. The slope of the T₁-filter between W and G is strongly negative (red line).

When the TI is increased further to a long TI, TI_l, the T₁-filter is displaced further to the right, as in Figure 4C (right) where W has a slightly higher signal than G, and the slope of the T₁-filter between them is mildly negative (red line).

Using the small change approximation of differential calculus, the contrast (difference in signal) produced by each T₁-filter from an increase in T₁ from W to G (horizontal green arrows in Figure 4A, 4B and 4C) is the size of this increase multiplied by the slopes of the respective T₁-filters (i.e., by their first derivatives, red lines). This contrast is shown by the vertical blue arrows in Figure 4 and is moderately positive in Figure 4A, highly negative in Figure 4B and mildly negative in Figure 4C. The slopes of the T₁-filters show the contributions of the sequence to the contrast in each example.

2.2. Subtracted IR (SIR) and divided Subtracted IR (dSIR) Bipolar Filters

Two conventional magnitude IR T₁-unipolar filters with different TIs, namely TI_short = TI_s and TI_intermediate = TI_i are shown in Figure 5A. The subtraction: first TI_s T₁-filter minus the second TI_i T₁-filter produces the subtracted IR (SIR) T₁-bipolar filter shown in Figure 5B. The vertical dashed lines at the null points of the two IR T₁-filters shown in Figure 5A divide the X axis in Figure 5B into the lowest Domain (lD), the middle Domain (mD) and the highest Domain (hD). In the mD in Figure 5B (between the two dashed lines) the size of the slope of the SIR T₁-bipolar filter is about double that of the IR T₁-filters shown in Figure 5A. This is because the slope of the SIR filter in its mD in Figure 5B is the positive slope of the TI_s filter in the mD shown in Figure 5A minus the negative slope of the TI_i filter in the mD also shown in Figure 5A.

The two IR T₁-filters shown in Figure 5A can also be added to give the Added IR (AIR) T₁-filter shown in Figure 5C. In its mD, which is bounded by the vertical dashed lines, the signal is reduced to about 0.20 compared with its value of 2 at T₁ = 0 (i.e., about one tenth).

Figure 6A shows a divided SIR (dSIR) T₁-bipolar filter in which the SIR T₁-bipolar filter in Figure 5B is divided by the AIR T₁-filter in Figure 5C i.e., $\frac{\mathrm{difference}}{\mathrm{sum}}$. The signal (S_dSIR) of the dSIR filter is given by:

$${\mathrm{S}}_{\mathrm{dSIR}}={\displaystyle \frac{{\mathrm{S}}_{\mathrm{TIs}}-{\mathrm{S}}_{\mathrm{TIi}}}{{\mathrm{S}}_{\mathrm{TIS}}+{\mathrm{S}}_{\mathrm{TIi}}}}$$

(2)

where S_TIs is the signal from the shorter TI filter and S_TIi is the signal from the intermediate TI_i filter.

The resulting dSIR T₁-bipolar filter (Figure 6A) shows a negative pole and a positive pole. Its mD shows a highly positive nearly linear slope which is about ten times larger than the slopes of the IR T₁-filters shown in Figure 5A. The dSIR filter has maximum and minimum values of ±1. (The contributions from mobile proton density and T₂ to conventional IR sequences cancel out with dSIR sequences which are therefore T₁ maps and the whole sequence can be accurately represented by its T₁-bipolar filters.)

Figure 6B compares the contrast produced by a conventional S_TIs IR T₁-unipolar filter (pink) to that from the SIR T₁-bipolar filter (blue) shown in Figure 5B from the same increase in T₁ (horizontal positive green arrow, DT₁). DT₁ is multiplied by the slopes of the respective S_TI IR and SIR filters (red lines) to produce the differences in signal DS, i.e., the contrast from each of them. This is shown by the vertical pink and blue arrows on the right. The SIR T₁-bipolar filter generates about twice the contrast (blue arrow) of the S_TIs IR T₁-unipolar filter (pink arrow) from the same increase in T₁, DT₁.

Figure 6C compares the contrast produced by the S_TIs IR T₁-unipolar filter (pink) to that produced by the dSIR T₁-bipolar filter shown in Figure 6A (blue). The increase in T₁ (horizontal positive green arrow, DT₁) is multiplied by the slopes of the respective S_TIs IR and dSIR filters (red lines) to produce the differences in signal DS, or contrast generated by the two filters. This is shown by the vertical pink and blue arrows on the right. For the same increase in T₁ (DT₁), the dSIR T₁-bipolar filter produces about ten times greater contrast than the S_TIs IR T₁-unipolar filter. The S_TIs IR T₁-filter is that of a conventional TI IR sequence such as MP-RAGE (magnetisation prepared-rapid acquisition gradient echo).

To produce the large increase in contrast shown in Figure 6C, the dSIR sequence is typically targeted at the small increase in the T₁ of normal tissue produced by disease (shown by the horizontal green arrow) positioned within the steeply sloping mD of the dSIR T₁-bipolar filter. This is done by choosing appropriate values of TI_s and TI_i. The target is often small increases in the T₁ of white matter. High contrast can also be produced by difference or change in T₁ within the lower part of the hD and the upper part of the lD where the dSIR T₁-bipolar filter has relatively steep slopes. More detail is available in reference [3].

2.3. Contrast at Tissue Boundaries

MRI tissue boundaries take different forms such as a gradual change in signal from one tissue to another as well as sharply defined high and low signal boundaries between tissues. In the boundary region between two pure tissues (such as between white and gray matter) the T₁s of voxels which contain mixtures of the two tissues typically span the range of T₁ values between those of the two pure tissues. If a narrow mD dSIR T₁-bipolar filter (e.g., with TI_s nulling normal white matter, and TI_i longer than TI_s but less than that needed to null gray matter) is used there are mixtures of the two tissues in voxels in the boundary region with intermediate T₁ values (T_1W,G) which correspond with the peak of the T₁-bipolar filter as shown in Figure 7. This produces a high signal boundary between white matter and gray matter. The dSIR T₁-bipolar filter shows much higher contrast than that produced between white matter and gray matter by a conventional white matter nulled IR sequence such as MP-RAGE (Figure 7). The mechanism shown in Figure 7 produces the high signal S_W,G at the boundary between normal white and normal gray matter shown in Figure 1B. High spatial resolution boundaries are also seen at the junction between CSF and white matter at ventricular boundaries, and can be seen at the boundary between gray matter and CSF with wide mD sequences [3]. The high and low signal boundaries on dSIR images are iso-T₁ contours.

2.4. T₁ maps and Qualitative - Quantitative MRI

To better understand the dSIR T₁-bipolar filter, a linear equation of the form y = mx + c can be used to approximate the filter in its mD. The equation is produced by fitting a straight line between the first and last points of the mD (i.e., first point x = $\frac{{\mathrm{TI}}_{\mathrm{s}}}{\ln 2}$ and y = -1, and last point x = $\frac{{\mathrm{TI}}_{\mathrm{i}}}{\ln 2}$ and y = +1). In the mD, the signal of the dSIR sequence S_dSIR, is given by:

$${\mathrm{S}}_{\mathrm{dSIR}}\approx {\displaystyle \frac{\ln 4}{∆\mathrm{TI}}} {\mathrm{T}}_1-{\displaystyle \frac{\mathsf{\Sigma }\mathrm{TI}}{∆\mathrm{TI}}}$$

(3)

where ΔTI = TI_i - TI_s (i.e., second TI minus first TI) which is positive, and ΣTI = TI_s + TI_i which is also positive. Note that because DTI is positive, the slope ${\displaystyle \frac{\ln 4}{∆\mathrm{TI}}}$ is positive. The offset is negative.

The expression in Eq. (2) illustrates four key features of the dSIR T₁-bipolar filter, firstly, the near linear change in signal (i.e., S_dSIR) with T₁ in the mD, secondly, the filter has a slope in the mD equal to ${\displaystyle \frac{\ln 4}{∆\mathrm{TI}}}$, thirdly the filter shows high sensitivity to small changes in T₁ when the size of ΔTI is small. When DT₁ is small, the size of DTI can be decreased to match it and so scale up the sensitivity of the filter. The reduction in DTI increases the steepness of the T₁-filter in the mD and thus the amplification of contrast produced from DT₁. This compensates for the small value of DT₁ until the sequence becomes SNR and/or artefact limited. This is not the case with conventional IR sequences where, if DT₁ is decreased, contrast decreases.

Fourthly, Eq. (3) can be used to calculate T₁ values in the mD so that:

$${\mathrm{T}}_1\approx {\displaystyle \frac{∆\mathrm{TI}}{\ln 4}}{\mathrm{S}}_{\mathrm{dSIR}}+{\displaystyle \frac{\mathsf{\Sigma }\mathrm{TI}}{\ln 4}}$$

(4)

The linear approximation is only valid in the mD. Also, it is assumed that TR is long compared to tissue T₁ values. An equivalent expression that allows for incomplete recovery of longitudinal magnetisation during TR can be formulated.

Outside of the mD in the lD and hD, the magnitude of the T₁-bipolar filter signal decreases towards zero at minimum and maximum values of T₁. T₁s in the mD occupy the full range of the display gray scale from black to white. T₁s from the shortest and longest T₁s in the lD and hD respectively only occupy parts of the display gray scale.

2.5. Log Then Subtracted Inversion Recovery (lSIR) Sequences

Another bipolar filter is the natural logarithm (ln) then subtracted inversion recovery (lSIR) filter [10]. The signal of this filter (S_lSIR) is half of the subtraction: ln short S_TIs T₁-filter minus ln intermediate S_TIi T₁-filter. The ln S_TIs and ln S_TIi unipolar negative T₁-filters are shown in Figure 8 and have sharper negative poles than those of unipolar S_TIs and S_TIi T₁-filters shown in Figure 5A.

Figure 9 shows a dSIR T₁-bipolar filter in blue and the corresponding lSIR T₁-bipolar filter with the same TIs in orange. The two filters appear similar in the lowest region of the lD and in the highest region of the hD as well as in the central region of the mD. The slope of the dSIR filter is essentially constant and equal to ${\displaystyle \frac{\ln 4}{∆\mathrm{TI}}}$. The magnitude of the slope of the lSIR filter is the same that of the dSIR filter at the centre of the mD but greater around the lower and higher nulling TI values. The lSIR filter asymptotically approaches negative and positive infinity at the two corresponding T₁s. The lSIR filter increases its contrast amplification as the change in T₁ from normal becomes smaller. Like the dSIR filter, the lSIR filter essentially eliminates the mobile proton density and T₂ dependence of the full IR sequence and so can be used to model the full sequence behaviour.

The lSIR filter is an inverse hyperbolic tangent of the dSIR filter in the mD (S_lSIR = atanh S_dSIR), and an inverse hyperbolic cotangent of the dSIR filter in the lD and hD.

From a practical point of view, the lSIR T₁-filter has 2-3 times the slope of the dSIR T₁-filter for very small differences or changes in T₁ around the null points and thus has 20-30 times greater contrast than conventional IR sequences for the same very small differences or changes in T₁. The maximum and minimum values of the lSIR filter are usually shown as ±2-3 (rather than ±infinity). This compares with values of ±1 for the dSIR filter. The low and high signal boundaries of the lSIR filter are narrower than those of the corresponding dSIR filter.

The lSIR filter shows a selective increase in slope, or sharpening, at iso-T₁ contours close to the nullpoints. It is not generalised edge enhancement of all boundaries on an image.

2.6. Composite (c) bipolar filters (T₁ as well as T₂, T₂*, D*, c and/or MT)

It is possible to introduce an attenuation filter S_OF (other filter) and apply it to one of the two IR filters used for dSIR T₁-bipolar filter imaging in Figure 5 and Figure 6. S_OF may equal e^–DTE/T2, e^–DTE/T2* or e^–DbD* which introduce T₂, T₂* and D* dependence respectively. This provides additional contrast to the T₁ contrast of the bipolar filter. When DTE equals zero, or Db equals zero, S_OF = 1. If S_OF is set to 0.5 and 0.25, the curves shown in Figure 10A and 10B result when using a narrow mD dSIR sequence (TIs = 350 ms and 500 ms). The nulling times are the same for all values of S_OF.

In Figure 10A attenuation of the first IR filter (with TI_s) is shown with S_OF set at 1 (blue), 0.5 (orange) and 0.25 (yellow). The yellow and orange curves are wider around the outside of the first (negative) pole at the first TI_s and are narrower and inside the second (positive) pole at TI_i. This results in a broadening and loss of contrast and lower signal white matter around the first negative pole as well as increased contrast and narrower boundaries between white and gray matter around the positive pole. S_OF can be set negative values to reverse the sign of the relevant contrast and make it synergistic with the T₁ contrast.

In Figure 10B, attenuation of the second IR filter (with TI_i) is shown. As S_OF is decreased from 1.0 to 0.5 and 0.25, the filter narrows around the first (negative) pole and widens around the second (positive) pole. The negative contrast produced for the same difference in T₁ is increased around the first negative pole. Composite (c) forms of the bipolar filters can be designated as cSIR, cdSIR, clSIR etc.

Susceptibility and magnetisation transfer can also be used to attenuate signals and produce supplementary contrast. The combination of T₁ and T₂* contrast may be of particular value in demonstrating the central vein sign and paramagnetic rim sign in multiple sclerosis (MS) as well as late sequelae of haemorrhage and fMRI in combination with perfusion.

2.7. Synthetic dSIR and lSIR T₁-Bipolar Filter Images

2.7.1. Synthesizing Narrower mD Images from Wider mD dSIR and lSIR T₁-Bipolar Filter Images

It is possible to synthetically create narrower mD dSIR images from wider mD dSIR images using Eq. 1 and the relationships illustrated in Figure 6A. The TIs of the narrower mD images are within those of the wider mD when using magnitude forms of the IR sequences.

2.7.2. Synthesizing dSIR and lSIR T₁-Bipolar Filter Images from T₁ Maps

dSIR and lSIR T₁-bipolar filter images with particular values of TI can also be synthesised from T₁ maps using Eq.1 and the relationships shown in Figure 6A, Figure 8 and Figure 9. T₁ and other tissue property maps (T₂, T₂*, D*) have linear TP-filters with maximum signal values at the high end of the tissue property X axis. As a result, CSF has high signals on the maps and this can dominate their appearance. The problem can be avoided when appropriate T₁-bipolar filters are applied to T₁ maps to create T₁-bipolar images in which CSF signal is reduced. The equivalent mapping using MP2RAGE acquisitions has also been described previously. While in principle the same contrast is obtained, there are wide discrepancies in the T₁s measured by different techniques suggesting T₁ is not independent of the method of acquisition. The unaccounted variance may mask small white matter abnormalities observed using dSIR images that were not previously seen with general purpose T₁ mapping.

2.7.3. Synthesizing T₂-, T₂*-, D*and c-Bipolar Filter Images Using Purpose Designed Bipolar Filters Together with T₂, T₂*, D* and c Maps

It is also possible to create TP-bipolar filter images from tissue properties other than T₁ using purpose designed synthetic TP-bipolar filters. These filters are typically based on the appearance of the dSIR T₁-bipolar filter shown in Figure 6A,C. They can have a linear function in their mD and a scaled reciprocal function (e.g., y = $\frac{\mathrm{a}}{\mathrm{x}}$) or similar function in their lDs and hDs. These functions join the linear function in the mD at signal values of -1 and +1, respectively. Synthetic TP-bipolar filters can then be used with T₂, T₂*, D* and c maps to create T₂-, T₂*-, D*-and c-bipolar filter images.

The lSIR inverse hyperbolic tangent and cotangent functions can also be used in the same way to create synthetic lSIR TP-bipolar filter images from tissue property maps.

Directly acquired T₁-bipolar filter images and synthetic T₁-, T₂-, T₂*-, D*-, c- and MT-bipolar images with different TPs can be multiplied together to produce synergistic multi TP-bipolar filter images. Under log then subtraction (lSIR) the multiplicative contrast become additive. The signs of the slopes of the TP-bipolar filters (negative or positive) can be matched with the signs of the changes in tissue properties (negative or positive) to ensure the contrast produced by the different tissue properties is synergistic [2].

2.8. Window Levels and Widths of Displayed Images

2.8.1. Conventional Changes in Window Level and Width of MR Images

When an image is displayed, the window level sets the brightness (signal level) and the window width sets the contrast (signal difference). Changes in the window level and width of images change their signals on the gray scale display from S to S_D and can be described using a high pass filter as seen in Figure 11A. This plots the display signal S_D against the image signal S. This is a signal (S) filter not a TP-filter. Contrast (the difference in signal between the S_Ds of P and Q) may be increased by narrowing the window width as shown in Figure 11B so that P and Q are now respectively shown at the bottom and top ends of the display scale. With narrow windowing, signals with values at the upper end of the X axis from Q and beyond are all shown with the same high value of S_D. As a result, there is no contrast between these voxels and they coalesce into blocks. This leads to a loss of anatomical coherence. The same also happens at the lower end of the S scale where values of S less than P have the same signal in Figure 11B and coalesce. This saturation of signals establishes a practical limit to how tightly images can usefully be windowed (i.e., how narrow the window width can usefully be made) and thus how much the contrast of the displayed image can be increased before the loss of anatomical coherence leads to a lack of credibility of the images. This is in addition to limits imposed by SNR considerations and image artefact levels.

2.8.2. dSIR Images

dSIR images can decrease DTI and so increase contrast. Maximum and minimum values are shown as high and low signal boundaries as in Figure 11C, T₁ values lower than the lower nulling T₁ value and greater than the greater nulling T₁ value do not appear on the same plateaux as with conventional narrow windowing in Figure 11B, but vary in signal because of the sloping regions in the lDs and hDs of the dSIR T₁-bipolar filter (Figure 11C). As a consequence, contrast is maintained and anatomical detail is preserved in all three Domains when DTI is decreased. As a result, contrast can be increased by decreasing DTI until it becomes SNR and/or artefact limited.

3. Methods

With approval from the New Zealand Health and Disability Ethics Committee (EXP 11360, 2022), and informed consent from each subject, MR scans were performed on four adult normal controls, seven adult patients with mild traumatic brain injury (mTBI), MS, methamphetamine substance use disorder, Grinker’s myelinopathy, Parkinson’s disease and rectal cancer metastasis. The research was conducted in accordance with the Declaration of Helsinki. 3T scanners (General Electric Healthcare Premier and Siemens Healthineers Skyra) were used. 2D IR FSE sequences were performed with a TI_s chosen to null the shortest T₁ normal white matter (or slightly shorter) and a longer TI_i chosen to produce narrow mD dSIR images targeted at small increases in the T₁ of white matter from normal as illustrated in Figure 6C. 3D wide mD dSIR images with a short TI_s and a long TI_l were also obtained [5]. Longer TE 2D IR images were acquired to produce cdSIR images. Positionally matched 2D and 3D T₂-FLAIR and susceptibility weighted filtered images were acquired as described in Table 1.

4. Illustrative Cases

4.1. Mild Traumatic Brain Injury (mTBI)

Conventional MRI usually shows little or no change in mTBI but narrow mD dSIR imaging frequently shows extensive high signal areas in white matter (the whiteout sign) (Figure 1). This may resolve within as little as two days or persist over years. It is generally attributed to neuroinflammation but oedema, demyelination and degeneration may also have a role.

In addition to the whiteout sign, there may be loss of contrast in the gray matter of the thalamus due to an increase in T₁. This is manifest as a low contrast appearance between the medial and lateral thalamus (Figure 12A) (arrows) (a grayout sign). After remission normal high gray white matter contrast is restored (Figure 12B) (arrows). Contrast between the lateral thalamus (arrows) and the posterior limb of the internal capsule (PLIC) is low in (Figure 12A) but very high in (Figure 12B). The low contrast between the thalamus and the PLIC in (A) is because of a reduction in signal in the gray matter of the lateral thalamus due to an increase in its T₁ in the hD as well as an increase in signal in the white matter of the PLIC due to an increase in its T₁ in the mD. This is reversed in (Figure 12B) where the normal high contrast boundary is restored.

Figure 13A shows a normal control with obvious contrast between the heads of the caudate nuclei and the adjacent CSF as well as between the cortex and CSF. Figure 13B shows a patient with mTBI who has a whiteout sign. There are grayout signs in the thalamus and putamen. In addition, contrast is lost between the heads of the caudate nuclei and CSF as well as between cortex and CSF which appear isointense. These are grayout signs. The patient has a combination of whiteout and grayout signs.

There may also be gray matter changes elsewhere in mTBI. The normal red nucleus has a relatively short T₁ resulting in its normal signal being mid-gray in the mD (arrows) (Figure 14A). It shows a higher signal due to an increase in T₁ in the case of mTBI (arrows) (Figure 14B).

4.2. Multiple Sclerosis (MS)

Focal lesions, as well as patchy white matter changes, may be seen in areas that appear normal on T₂-wFSE images in a patient in remission (Figure 15) (compare with normal appearance in Figure 1B). In another case during a relapse, one lesion is seen on the T₂-FLAIR image in Figure 16A (long arrow). This lesion is also seen in Figure 16B (long arrow). There are an additional six lesions (small arrows) in Figure 16B. Some of MS lesions in Figure 16B have high signal boundaries. This can be due to a large increase in T₁ in the lesion or a decrease in the abnormal T₁ of a lesion due to the presence of paramagnetic free iron. Some of the lesions with high signal boundaries shown in Figure 16B have paramagnetic rims on the filtered susceptibility weighted images (arrows, Figure 16C).

In addition, there are widespread abnormal areas in white matter which are only seen on the dSIR images (Figure 16). These changes are typically bilateral, symmetrical and have an increased signal and have the features of a whiteout sign (Figure 16B) and to date have only been seen in MS patients during a relapse.

Composite T₁ and T₂ cdSIR images may show higher contrast than corresponding dSIR images (Figure 17A and 17B).

In the spinal cord in another patient with MS, the T₂-FLAIR image only shows an ill-defined smudge (arrow) (Figure 18A). The corresponding wide mD dSIR image (Figure 18B) shows an extensive, well defined, high contrast abnormality (arrows). Another lesion is seen in the medulla on the dSIR image (arrow) but not on the T₂-FLAIR image.

4.3. Methamphetamine Substance Use Disorder

Patients with methamphetamine substance use disorder may show a heterogenous pattern of white matter abnormalities with dSIR sequences but they may also show clearly defined whiteout signs and these can remit with continued abstinence (Figure 19) (compare with normal appearance in Figure 1B). The situation may be confounded in the case shown by a previous mTBI.

4.4. Delayed Post-Hypoxic Leukoencephalopathy (Grinker’s Myelinopathy)

This is thought to be a rare syndrome in which classically patients make an initial recovery after a hypoxic and/or ischemic episode, and then deteriorate with severe neurological signs such as Parkinsonism and akinetic mutism. Conventional MRI shows widespread abnormalities in the white matter of the cerebral hemispheres. In this type of clinical situation, it is possible to see extensive abnormalities in white matter with dSIR sequences where no abnormalities are seen with conventional sequences [7]. The patients typically have cognitive symptoms of less severity than in classical descriptions. This less severe form of Grinker’s myelinopathy may be much more common than the classical form but not be recognised using conventional MRI sequences.

4.5. Parkinson’s Disease

Parkinson’s disease may show more obvious bilaminar signs in the cortex than in age matched controls (i.e., an increased signal in the outer layer of the cortex) with narrow mD dSIR sequences (white arrows) (Figure 20). The inner higher signal is from the boundary between white matter and gray matter and the next layer outwards is lower signal in the inner cortex. The next outer layer beyond this is the higher signal layer in the outer cortex.

Bubble signs in which circular areas of similar size are seen in the gray matter in the basal ganglia and thalamus can also be seen (e.g., black arrows) (Figure 20).

4.6. White Matter Associated with Cerebral Tumours

In cases of cerebral tumours, extensive white matter changes have been seen in areas that appeared normal on T₂-FLAIR images after chemotheraphy (Figure 21A and 21B). When typical radiation or chemotherapy changes have been seen on T₂-FLAIR images, additional changes have been observed in the form of whiteout signs.

4.7. Normal Control and MS Patient with dSIR and lSIR Images

dSIR and lSIR images (Figure 22A and 22B) are compared in a 46-year-old male normal control. White matter gray matter boundaries and the bilaminar cortex sign (arrows) are seen with higher contrast and higher spatial resolution on the lSIR image. Bubble signs are also better seen in the thalamus and putamen on the lSIR image. A very small decrease in T₁ through the sharp peak of the lSIR T₁-bipolar filter results in finer boundaries and narrower margin bubble signs with the lSIR T₁-bipolar filter compared to the dSIR T₁-bipolar filter.

In a 41-year-old female patient with MS, the dSIR image (Figure 23A) shows a blurred leukocortical lesion in the right medial frontal region with no evidence of a white matter/gray matter boundary within it. The matched lSIR image (Figure 23B) shows a disrupted high signal boundary between white matter and gray matter within the lesion. Profiles (plots of signal against position in mm) through the lesion at the level shown by the arrows for the dSIR (blue) and lSIR (orange) images shows a higher signal and steeper slope for the lSIR image (Figure 23C). The spatial resolution of the contrast i.e., change in signal with change in position is generally higher on the lSIR image.

5. Discussion

5.1. UHC MRI Using Bipolar Filters

UHC MRI is a term used to describe MRI techniques which show much greater contrast than conventional state-of-the-art MRI images while having similar spatial resolutions and comparable acquisition times. This is achieved with no increase in static or gradient magnetic field. UHC MRI using bipolar filters employs sequences existing on most MRI machines with minimal image processing. It can be implemented in a very short time at very little cost.

UHC MRI is distinguished from ultra-high field MRI which uses static magnetic field strengths of 7T or higher to improve image signal-to-noise ratio. This improvement may be used to increase contrast, spatial resolution and/or the speed of MRI scans [11].

UHC MRI is also distinguished from ultra-high spatial resolution MRI where typically increased gradient strength is used to improve spatial resolution [12].

The three main types of directly acquired bipolar filter (BLAIR) used to achieve UHC MRI in this paper are summarised in Table 2 with some of their variants. Their signal equations and other relevant functions are included in Table 3. This table also provides information for synthetic imaging.

The dSIR sequence is the BLAIR sequence most used to date. It has been validated in quantitative phantom and human studies [13,14].

While the emphasis in this paper has been on white matter in the mD and grey matter in the hD, very high contrast can also be seen in the central grey matter of the brain when this is in the mD rather than in the hD. In addition, iron containing tissues have only been studied with dSIR using the single tissue property T₁, not the composite sequence cdSIR using two tissue properties T₁ and T₂*.

Understanding the contrast produced by TP-bipolar filter sequences is greatly helped by use of their TP-filters. These filters relate differences or changes in tissue properties to contrast using their slopes and explain signal and contrast patterns that can otherwise appear inexplicable using conventional approaches [8,9].

Artefacts from too high a value of TI_i, misregistration, partial volume effects and other causes are described in reference [5]. Means of avoiding these and/or reducing their effects are included.

5.2. Tissue and Fluid Boundaries

dSIR and lSIR images are characterised by sharply defined high contrast, higher spatial resolution boundaries between white matter and gray matter as well as between white matter and CSF, and between gray matter and CSF. The site of the boundaries as well as their width can be changed by varying the TIs of the sequence [5]. In addition, there are well defined low signal (dark) boundaries between white matter, gray matter and CSF as modelled by TP-bipolar filters.

High signal in plane boundaries on dSIR images usually have a uniform and consistent appearance although these are subject to partial volume effects and may simulate lesions particularly with 2D images acquired with relatively thick slices (e.g., 2-4 mm). Through plane partial volume effects also produce high signal from boundaries and these are more prominent with thick slices.

A systematic treatment of boundaries including variation in signal with position using TP-filters, the partial derivative change in T₁ with tissue fraction and the partial derivative change of tissue fraction with position is described in reference [5]. Using this approach, differences in signal (i.e., contrast) can be related to differences in position within the boundary region. The dSIR and lSIR filters produce higher contrast and higher spatial resolution of the contrast at boundaries between tissues and fluids. The boundaries are specific and located at iso-T₁ contours. They are not part of a generalised pattern of edge enhancement.

5.3. Hybrid Quantitative and Qualitative Imaging

dSIR sequences produce single images that can be used both quantitatively and qualitatively. The images show high contrast and this can be used for conventional qualitative image interpretation. The images are also T₁ maps so they can be used to directly measure T₁ values in regions of interest placed on them for quantitative studies. In comparison with the conventional approaches to T₁ quantitation which use separate images for qualitative interpretation and T₁ mapping, dSIR images: (i) do not require working with images of two different types; (ii) allow precise placement of ROIs in relation to lesions on the images used for radiological interpretation, and (iii) require no extra time for additional acquisitions.

T₁ values of dSIR sequences have shown comparable accuracy to conventional T₁ mapping in the mD but, as expected, differences in the lD and hD [13,14].

5.4. Magnetisation Transfer (MT)

With 2D multislice acquisitions, there may be incidental magnetisation transfer (MT) effects from off-resonance 180° or similar pulses used during FSE acquisitions. Using two pool modelling, MT decreases the observed mobile proton density in the free pool but also decreases the observed T₁ of the free pool in proportion to the reduction in observed mobile proton density [15]. This reduction may be quite substantial and decrease normal observed T₁s (T_1obs) by as much as 50%. In general, in disease MT effects are decreased so the reduction in T_1obs in diseased tissue due to MT is generally less than that in normal tissue. This is manifest as an apparent increase in T_1obs in diseased tissue relative to normal tissue in addition to any increases in T₁ in diseased tissue for other reasons e.g., pathological change such as oedema.

2D FSE images with higher echo train lengths (ETLs) require more 180° pulses and thus produce a corresponding increase in MT effects during multislice acquisitions. These produce a greater reduction in values of T_1obs and so need shorter nulling TIs. MT effects are less with gradient echo acquisitions as usually used with 3D acquisitions. As a result, T_1obs may be longer with 3D gradient echo acquisitions than with 2D FSE acquisitions and so their nulling TIs may need to be correspondingly longer. The contrast between normal and abnormal tissues may also be lower with gradient echo acquisitions.

MT following IR can also be used as an attenuating filter S_OF in composite bipolar filters.

5.5. Synthetic T₁-Bipolar Filters

Synthetic bipolar filters can be of two types as shown in Table 2. The first uses Eq. 1 and the relationships shown in Figure 6, Figure 8 and Figure 9 to synthesise dSIR and lSIR images with different TIs from two directly acquired images. The second type uses a synthetic TP-bipolar filter which may be the same or similar to the dSIR and lSIR filters and applies these to tissue property maps. This approach has two aspects: (i) acquiring the tissue property map which should be of high quality in the tissue property Domains or parts of Domains of interest, and (ii) using a visualization function such as a bipolar filter to increase contrast without saturating voxel values. These two aspects are incorporated in directly acquired dSIR and lSIR imaging.

5.6. Signs Produced with dSIR Sequences

5.6.1. The Whiteout Sign

This is a generalised bilateral symmetrical increase in signal in white matter of the cerebral and cerebellar hemispheres as well as the brainstem [1]. The increase in signal follows the pattern of normal white matter signals and can involve all, or almost all, of the white matter in a particular slice. It has specific features such as sparing of the anterior and posterior central corpus callosum (genu and splenium) as well as peripheral white matter in the cerebral hemispheres (Figure 1, Figure 12, Figure 13, Figure 14, Figure 19, Figure 21). The white matter signal can increase to that of the high signal boundary between white and gray matter and can be divided into five grades [1]. It is due to widespread, small increases in T₁ and is thought to be particularly associated with neuroinflammation but may also be due to oedema, demyelination, degeneration and other causes. It has also been seen in mTBI, hypoxic/ischaemic injury to the brain, multiple sclerosis and tumours with/without treatment.

5.6.2. Grayout Signs

With grayout signs there is maybe a loss of contrast in gray matter such as is seen in the thalamus and basal ganglia after mTBI (Figure 12 and Figure 13), or a loss of contrast between gray matter and white matter, or between gray matter and CSF (Figure 13B). Grayout signs are generally more subtle than the whiteout sign. They are associated with an increase in T₁ in gray matter.

In young subjects, the normal lateral thalamus gray matter (TG_lat) has a shorter T₁ than the normal medial thalamus gray matter (TG_med) (upper horizontal negative solid green arrow). This leads to higher signal in the lateral thalamus with a narrow mD dSIR sequence (first vertical blue arrow) (Figure 24). The T₁ of the lateral thalamus may increase in disease (middle horizontal positive green striped arrow in Figure 24) which produces a loss of contrast with the medial thalamus (blue circle). With reversion back to normal on recovery, the T₁ may decrease back to normal (lowest horizontal negative green arrow) restoring contrast (second vertical blue arrow).

The whiteout sign may be accompanied by grayout signs in conditions such as mTBI and the case of metastatic rectal cancer described in this paper. The term post-insult leukoencephalopathy syndromes (PILS) used in reference [1] only refers to whiteout signs after mTBI, Grinker’s myelinopathy etc. A term that includes both the whiteout sign and grayout signs as well as the possibility of ongoing effects (rather than just post-insult effects) is reactive encephalopathy (RE). Depending on the observed features (presence/absence of grayout signs), the pattern may be described as PILS/RE. Experimental studies to determine the histological origins of the signs are in progress.

5.6.3. The Bilaminar Cortex Sign

This is an increase in signal in the outer layer of the cortex which is barely seen in young adults but becomes more obvious with increasing age as well as in Parkinson’s disease. It is seen with narrow mD dSIR images in which there is a high signal at the white matter gray matter junction, a lower signal layer in the inner cortex and a higher signal layer in the outer cortex (Figure 20 and Figure 22). The higher signal generally corresponds to layers 1-3 and the lower signal to layers 4-6 of the cortex. The increase in signal is usually most obvious at the crest of gyri and to a lesser extent in the banks of sulci. It may be obscured by partial volume effects particularly on 2D images of 4 mm thickness compared with the estimated 2-4 mm thickness of the cortex. The sign may be due to increased free iron content with a decrease in T₁ of the normal cortex with increase in age, with an exaggeration of this in Parkinson’s disease [16]. It is distinguished from the double cortex sign [17] which is due to iron deposited in a subcortical location. A bilaminar cortical appearance has been seen with MP2RAGE sequences at 7T after detailed image processing and has been attributed to differences in myelin [18]. The bilaminar cortex sign differs from the high signal that can be seen at the cortical margin on T₂-FLAIR images. This signal is attributed to increased T₂ relative to brain in cortical veins/pia arachnoid (as opposed to a decreased T₁ in the bilaminar cortex sign). It is usually more evident on 2D T₂-FLAIR images with longer TIs and TRs than 3D T₂-FLAIR images though the latter may have very long effective TEs. It can be present in young subjects who do not show a bilaminar cortex sign.

5.6.4. Bubble Signs

With the narrow mD dSIR sequence nulling white matter, bubble signs are seen with an increase in T₁ that crosses the high signal boundary (“overshoots”) and enters the hD (Figure 16B) [5]. There is an outer high signal margin and a lower signal central region [3]. Bubble signs may also be seen in the gray matter of the thalamus and basal ganglia with narrow mD dSIR sequences when the T₁ in the gray matter decreases and crosses the high T₁-bipolar filter peak. Bubble signs become more obvious with age and are seen in Parkinson’s disease. The decrease in T₁ in gray matter sufficient to cross the high signal boundary of narrow mD dSIR sequences is illustrated in Figure 20 and probably reflects heterogeneous distribution of free iron. Bubble signs may also be produced in MS by release of free iron at the rim of lesions decreasing the T₁ in abnormally increased T₁ lesions.

Figure 25 illustrates the origin of the bubble sign in the thalamus. The T₁ of lateral gray matter is decreased from normal (TG_latnorm) to abnormal (TG_latab). In doing so, it passes through the peak signal where there is a partial volume effect between TG_latnorm and TG_latab. This results in a high signal on the periphery and a lower signal centrally in the bubble as shown by the vertical blue arrows in Figure 25.

5.6.5. Primary Cerebral Hemisphere Cortices

The primary motor, somato-sensory and visual cortices have relatively greater myelin than elsewhere in the cortex, and this results in a shorter T₁ and so higher signal in the hD relative to cortical signal elsewhere when using narrow mD dSIR sequences.

5.7. Clinical Use of T₂-FLAIR and Tissue Property BipoLAr fIlteR (TP-BLAIR) Sequences

T₂-FLAIR and TP-BLAIR sequences are complementary. The T₂-FLAIR images show contrast due to larger changes in T₂ and TP-BLAIR sequences such as dSIR show abnormalities due to smaller changes in T₁ in white and/or gray matter in areas that appear normal or near normal with conventional T₂-FLAIR sequences (e.g., Figure 16A,B). In many diseases there are concurrent increases in both T₁ and T₂ so that the TP-BLAIR sequence to match the T₂-FLAIR sequence does not have to be specifically sensitive to T₂.

Other bipolar sequences can be used besides directly acquired dSIR sequences. These include synthetic dSIRs as well as T₂ and other tissue property synthetic TP- bipolar filters. Directly acquired T₁-bipolar filter sequences may be made sensitive to T₂, T₂* and D* as well as T₁ as composite bipolar filters e.g., T₁,T₂-BLAIR. There is an advantage in T₁-BLAIR imaging with dSIR sequences since they can be directly acquired and do require acquisition of a tissue property map.

5.8. Other Sequences

5.8.1. The Double Inversion Recovery (DIR) Sequence

The DIR sequence multiples two IR sequences together and is one of the multiplied added subtracted and/or divided IR (MASDIR) group of sequences [5]. It has a unipolar T₁-filter as well as T₂ and mobile proton density filters. Initially, the two IR sequences were used to null fat and CSF [19] but in later versions either white or gray matter was nulled and so was CSF [20]. Lesions which increase T₁ and T₂ contrast produce synergistic contrast. When white matter is nulled with the conventional DIR sequences, this can be of particular value for imaging lesions of the cerebral cortex.

In a study using a gray matter and CSF nulled DIR sequence in patients with MS so that only white matter signal remained, Tillema et al. found a dark rim around lesions in white matter with longer T₁s and this helped in the diagnosis of MS [21]. The rim was due to nulling of T₁s in the boundary region between normal white matter and lesions which was evident if the T₁ of the MS lesions was increased beyond the T₁ of nulled gray matter. This was seen more often in MS than other diseases. The nulling effect is dependent on the T₁ of the mixture of tissues matching the first nulling TI of the DIR sequence. It corresponds to the high signal bubble sign seen in white matter (Figure 16B). Release of paramagnetic free iron may also have a role.

5.8.2. Magnetisation Prepared 2 Rapid Acquisition Gradient Echo (MP2RAGE) [22]

This sequence multiplies the signals of two IR sequences together and divides this by the sum of the squares of the signals from the two sequences. Complex multiplication is employed. Signal values vary between ± ½. It is a negative unipolar T₁-filter for brain and has a moderate negative slope between white matter and gray matter with a shallower positive slope between gray matter and CSF (Figure 26, blue curve labelled FLAWS-uni which is identical with MP2RAGE). The sequence places white matter at the upper end of the display scale, gray matter at the lower end of the display scale and CSF at an intermediate level which is similar to the divided reverse SIR (drSIR) sequence but the reverse of the dSIR sequence.

5.8.3. Fluid and White Matter Suppression High Contrast (FLAWS-hc), FLAWS- High Contrast Opposite (FLAWS-hco) and FLAWS-Minimum (FLAWS-min) [23,24]

The FLAWS-hc and FLAWS-hco sequences have the same general mathematical form as the dSIR and drSIR sequences i.e., subtraction of two IR sequences divided by their sum i.e., $\frac{\mathrm{difference}}{\mathrm{sum}}$, but differ in important ways: firstly, the TIs used are widely separated as opposed to dSIR and drSIR sequences where the TIs are usually narrowly separated in order to specifically target small differences or changes in T₁ in tissues. Secondly, complex multiplication is used and the images are in phase-sensitive form not magnitude form. In Figure 26 the FLAWS-hc filter (green) has a positive slope over a very wide T₁ domain and the FLAWS-hco filter (orange) has a negative slope over the same very wide Domain. The magnitude of the slopes of the two filters are generally greater than that of the FLAWS-min/MP2RAGE filter. The monotonic form of the FLAWS-hc and FLAWS-hco T₁-filters is strikingly different from the bipolar form of dSIR and lSIR T₁-filters which have well defined, sharp discontinuities at their null points due to the use of magnitude reconstruction. They also have steep positive slopes within narrow mDs rather than the broad lower magnitude slopes of the FLAWS-hc and FLAWS-hco filters over wide T₁ Domains (Figure 26).

The FLAWS-min filter is the lower signal from two IR T₁-filters, one nulling white matter and the other nulling CSF. This is divided by the sum of the signals from the two filters and has a maximum value of a ½ and a minimum value of zero for the brain. It follows the shorter TI nulling IR filter in the lower part and the longer TI nulling IR filter in the higher part of the T₁ Domain. It is a positive unipolar filter with the lowest signal nulling white matter, a peak at a T₁ just greater than the T₁ of gray matter, and CSF as zero signal (Figure 26). It has similarities to the narrow mD dSIR sequence but has a lower display range and a lower slope. Müller et al. described a halo sign when imaging MS lesions in the cortex with the FLAWS-min sequence (Figure 5 in reference [25]). This is due to an increase in cortex T₁ in lesions passing through the peak of the FLAWS-min filter into longer T₁ regions. The slope of the T₁-filter of the FLAWS-min sequence around its maximum value is relatively low and this may account for the greater width of the halo sign compared with the width of the bubble sign found with the narrow mD dSIR sequence when there is an increase in T₁ through the peak of that sequence (e.g., Figure 16B). There are also high signal boundaries between ventricular white matter and CSF as well as between white matter and a periventricular lesion with the FLAWS-min sequence (in Figure 5, reference [25]) as expected from its T₁-filter.

A similar pattern is seen in the leukocortical lesion shown in Figure 2B of reference [26] using T₁w-FLAWS which is the same as FLAWS-min. However, the cortical lesion shown in the same figure imaged with T₁w-FLAWS shows low contrast with the surrounding normal gray matter. Increased signal is seen at the boundary between gray matter and CSF. These features are consistent with Figure 26 (blue curve for FLAWS-min). FLAWS-min images do not show high signal between white matter and gray matter because the peak signal on the FLAWS-min T₁-filter is not between these two tissues. If the second nulling TI (of CSF) is reduced, the FLAWS-min sequence becomes more like a narrow mD dSIR filter but with lower magnitude slopes.

In summary, the MP2RAGE and FLAWS T₁-filters are unipolar or monotonic, not bipolar. They have fixed TIs and wide T₁ Domains with lower slopes than narrow mD dSIR T₁-bipolar filters in their mDs. The FLAWS-uni/MP2RAGE T₁-filter has a moderate slope, reduced CSF signal and shows white and gray matter at the upper and lower ends of the display scale. FLAWS-hc has a higher slope than FLAWS-uni/MP2RAGE, with CSF very high signal and a wide display range from WM to CSF. FLAWS-hco also has a higher magnitude negative slope than FLAWS-uni/MP2RAGE with CSF very low signal and a wide display range from CSF to white matter. FLAWS-min has a positive T₁-unipolar filter with a moderate slope and peak signal at a T₁ just greater than that of gray matter. The T₁-filters shown in Figure 26 provide a succinct and accessible way of comparing the signal levels and contrast performance of these sequences.

5.8.4. White Matter Nulled MP-RAGE [27] and Fast Gray Matter IR (FGATIR) [28]

These are single IR sequences that null white matter so that most of the remaining signal present in the brain is from gray matter. They have negative unipolar T₁-filters. The slopes of their T₁-filters are shown in Figure 6B and 6C when TI is chosen to null white matter. Small differences or changes in white matter from normal show much less contrast with white matter nulled MP-RAGE than with white matter nulled narrow mD dSIR sequences (Figure 6C). Boundaries between white matter and gray matter also show higher contrast with narrow mD sequences (Figure 7).

5.8.5. 3D-Edge Enhancing Gradient Echo (3D-EDGE) [29] and EDGE-MP2RAGE [30] Sequences

The EDGE sequence has a single IR gradient echo with a negative unipolar T₁-filter and a TI chosen to produce zero signal at the boundary between white and gray matter with equal signals in each tissue. It uses magnitude reconstruction. The boundary contains voxels with a mixture of the two tissues and a T₁ between those of white and gray matter. It is of value in localising boundaries and diagnosing focal cortical dysplasia. EDGE-MP2RAGE acquires two separate images, the first of which is nulled in the same way as for the 3D-EDGE sequence. FGATIR, 3D-EDGE and EDGE-MP2RAGE images can be synthetically created from MP2RAGE derived T₁ maps [31].