POST-OPERATIVE IMAGING of the Shoulder MRI

Anatomic repair of the labrum and capsule using metallic suture anchors is being increasingly employed in glenohumeral instability using an arthroscopic approach[28]. On post-operative MR imaging, susceptibility artifacts

Normal post-operative appearance after arthroscopic suture-anchor repair of Bankart lesion. Oblique sagittal (A) and axial (B) T2-weighted TSE fat-suppressed image reveals the three suture-anchors in place (arrows). No fluid is seen between the labral margin and the opposed labrum and joint capsule.
(Figure ​ from the metallic implants may degrade the image quality. A few important points should be kept in mind to overcome this problem: gradient echo sequences should be avoided and replaced by spin echo sequences when possible; fast spin echoes are preferable over standard spin echo sequences; and inversion recovery sequences should be preferred over chemical fat suppression. After an anatomic apposition of the labrum to the articular margin in suture-anchor repair, no hyperintensity should be visible between the two. MR arthrography is more useful in post-operative shoulders as a problem solving tool in suspected recurrent labral tear. Contrast-enhanced T1W sequences should always be acquired in addition if there is a suspicion of septic arthritis[29].

Non-anatomic repairs (Putti-Platt repair, Bristow-Helfet procedure) are usually not preferred for primary instability surgery. Following capsular shift or shrinkage procedures, thickening of the joint capsule can be visualized on imaging.

Complications during arthroscopic repair include inadvertent injury to the axillary nerve (lying in close relation to the inferior joint capsule) and subscapularis muscle injury, hematoma, infection, septic arthritis, heterotopic ossification.

MRI protocols and disease pathology for HIP MRI

Boutin described three major MR protocols that apply to patients who are sent for hip imaging: one for routine screening, one to assess for internal derangement, and one to reduce artifacts in patients with prosthetic hardware.
For the clinical indication of avascular necrosis (AVN) in a screening setting, Boutin recommended a large field-of-view (FOV, 46-40 cm) to screen both hips in the coronal and axial planes, while using a smaller FOV to take a closer look at the affected hip in the sagittal plane (≤ 20-40 cm).
The causes of AVN can either be traumatic injury (hip subluxation) or a nontraumatic systemic problem, such as thromboembolic abnormalities. Those with systemic AVN are at risk for osteonecrosis in several other sites as well, Boutin said.
The sensitivity, specificity, and accuracy of MRI in AVN has held fast at 90% or more in several studies, he noted, adding that many difference sequences can be used for screening. He cited a protocol of coronal T1-weighted and fast spin-echo (FSE), axial T2-weighted and FSE, and sagittal T1-weighted as an example of one that is often used.
Common MRI findings for AVN include a demarcated zone of altered signal intensity extending to the superior subchondral bone plate, a double-line sign on T2-weighted images, and a serpentine border on low signal intensity images.
When reporting to orthopedic specialists, Boutin said the most important hallmarks of AVN to relate are femoral head collapse, size of AVN, and acetabular changes.
Moving on to the assessment of internal derangement, Boutin said that high-resolution, unilateral hip imaging is a must for diagnostic success. He recommended using a surface coil along with a small FOV (14-16 cm), section thickness of 3-4 mm, and a "negligible interslice gap."
"Just like we would never think of looking for a meniscus tear in the knee by scanning both knees at the same time, if we are looking for an internal derangement of the hip, we shouldn't be scanning both hips at the same time," he said.
MR arthography (MRA), with an average of 10 mL of injected gadolinium (off-label use), is another option and is generally preferred by radiologists for assessing the hip labrum and articular cartilage, Boutin said. MRA does require STIR images to assess extra-articular abnormalities that may not be seen on T1-weighted imaging, he explained.
"The added benefit of MRA is that when you have the needle in that joint, you can concurrently inject local anesthetic and confirm that the pain generator is in the hip," Boutin said. "If the pain goes away after injection of the local anesthetic, the presumption is that the pain generator is in the hip. If the pain doesn't go away, then you really have to consider the possibility of pain being referred to the hip region from another place such as the spine."
Among the various causes of labral derangements is developmental dysplasia of the hip (DDH) and femoroacetabular impingement (FAI). FAI generally strikes people under the age of 40 and is considered a major cause of osteoarthritis, Boutin explained. There are two types of FAI, femoral FAI (also known as cam FAI) and acetabular FAI (pincer FAI), and most cases are a combination of both.
On MRI, the main criterion for a labral tear is a linear hyperintense signal contacting the labral surface, Boutin wrote in the course syllabus. This signal can appear either at the labral-acetabular junction or the labrum itself. If the labra appears with enlarged or blurred margins, or demonstrates indeterminate signal intensity, then degeneration has most likely occurred.
"It's helpful to know where labral tears and derangement occur," Boutin said. "Commonly, they occur in the anterior or anterosuperior portion of the acetabular labrum. Coronal images commonly don't show the tear. Axial images often don't show the tear. Oblique axial images should show the tears with an 88% sensitivity. This is the best way to see these labral detachments."
MRA is currently considered more accurate than standard MRI for diagnosing labral tears, but detection depends on the size of the labral lesion. Also, a serious pitfall to watch out for on MRI is the misdiagnosis of sublabral sulcus as a tear. On MRI, a sublabral sulcus will manifest with smooth edges and the absence of adjacent degenerative changes.
Finally, there is a protocol for patients with metal implants, a situation that was once considered a contraindication for MR exams, Boutin said. However, MRI has proved to be most suitable for investigating the causes of pain after total hip arthroplasty, such as a loose component, stress fracture, or nerve compression.
Boutin recommend the following low-field MR protocol for reducing metallic susceptibility artifacts: FSE imaging with minimal interecho spacing, STIR sequence, and no gradient-recalled echo (GRE) sequence.
He also outlined a newer protocol called MARS, or metal artifact reduction series, that advocates the following adjustments: increase receiver bandwith and number of excitations, increase spatial resolution, and direct misregistration artifacts away from the areas of diagnostic interest.
With misregistration artifacts, "you have control over what is called the frequency encoding direction," Boutin explained. "It turns out that the misregistration artifacts preferentially occur in this frequency encoding direction. For example, if you want to see medial and lateral to an implant, you can direct the frequency coding direction in an inferior to superior direction."

Thoracic aorta MRI techniques

Thoracic aorta anatomy is complex, variable and the blood flow can be fast or slow. As a result, no single protocol will be suitable for all patients. It is necessary to customize the exam based upon the indication, age, cardiovascular status and anatomy.

In general pediatric patients and young adults have very fast flow which allows the aorta to be well seen on spin echo and time-of-flight sequences. In these patients the black blood, T1 weighted spin echo sequences with EKG gating may be sufficient. Use at least a minimum full echo and no gradient moment nulling (no flow compensation) to achieve suffcient "black blood" effect. Older adult patient generally fall into one of two categories. The first category are those with know aortic aneurysm or dissection and the only clinical issue is to determine if the aneurysm or false lumen is increasing in size. To measure aortic diameter, a simple protocol including Coronal T1, Axial T1 and Sagittal oblique T1 spin echo sequences is adequate. The second category are all the other patients where more precise vascular anatomy and lumenal detail involving both aorta and branch vessels must be imaged. For this second category of patients, 3D Gd:MRA is essential.

Sagittal 3D Gd:MRA: If you have a slow scanner and only the only the aorta and proximal great vessels need to be imaged, consider a sagittal 3D Gd:MRA.The sagittal acquisition eliminates the problem of wrap-around artifact from the arms along side the patient and allows coverage of the aorta with fewer slices. With sagittal acquistion you can speed up the scan by using rectangular FOV or you can reduce the FOV to maximize resolution.

Coronal 3D Gd:MRA: But if you need to image the subclavian or renal arteries, a coronal acquistion for the 3D Gd:MRA is preferred. This requires a state-of-the-art scanner with fast gradients to cover the anatomy with sufficient resolution within a breath hold. Start with a Sagittal spin echo locator, then axial T1, then coronal 3D Gd:MRA followed by axial 2D TOF post gadolinium. If the renal arteries are an issue (especially in patients with hypertension) then 3D phase contrast of the renal arteries can be added on at the end to take advantage of the extra SNR from the gadolinium that was administered

Chest MRI Protocols

Series 1: Scout

The scout is acquired as a free-breathing half-Fourier acquired single-shot turbo spin echo (Siemens HASTE) or single-shot fast spin echo technique (GE SSFSE). During this 25-s scan, 28 slices are acquired: 8 in the sagittal plane, 5 in the coronal plane, and 15 in the axial plane.

Series 2: Coronal T2 breath-held

In addition to its role as a screen for pathology, this series can be used as a reference for prescribing subsequent breath-held sequences. HASTE or SSFSE is typically the default sequence, allowing complete chest coverage in a single breath-hold. If further detail is desired, a 2D multislice multibreath-hold turbo spin echo (Siemens TSE) or fast spin echo (GE FSE) can be employed. We currently use a periodically rotated overlapping parallel lines with enhanced reconstruction (PROPELLER) technique acquired in about 5-6 breath-holds of about 17-23 s. BLADE is the Siemens proprietary variant of PROPELLER. We have found that the central k-space oversampling and inherent motion correction properties of this technique result in less motion artifact from the heart and subtle respiratory modulations as well as increased sharpness of the lung/pleural interface. Analogous observations in the pelvis have been reported. [8] Radial artifacts can be minimized by appropriate attention to blade width and oversampling parameters.

Series 3: Coronal 2D bSSFP, free-breathing

This series is a nonfat-saturated 2D multislice balanced steady state free precession (bSSFP) sequence. These image acquisitions are often extremely useful, providing exquisite anatomic information and soft tissue contrast as well as dynamic information on diaphragmatic excursion with respiration. Occasionally, relative tumor mobility can be assessed on these image acquisitions. This 2D technique of evaluating lung motion in both healthy volunteers and in patients with intra- and extra-pulmonary disease has been compared with other investigational 3D MRI techniques [9] with reported good correlation. In patients who cannot receive intravenous gadolinium, bSSFP images often provide an adequate look at the central vascularity.

Series 4: Navigator scout

The purpose of this series is to optimize placement of a 2D navigator for subsequent navigator-triggered acquisitions. Navigator Scout images are HASTE/SSFSE acquisitions, which, at first glance, may seem like a redundant series to the Scout Series. We have observed that: (1) initial anxiety can lead to erratic diaphragmatic motion, which is generally allayed this far into the examination, making tracking of the right hemi-diaphragm more regular at this point of the examination, and (2) we can obtain a more reliable location of the posterior aspect of the dome of the liver on an axial slice, which is an optimal place for navigator placement. Some patients who have had surgery on the right side may have suboptimal right hemi-diaphragmatic excursion, and in those instances, we have been successful in placing the navigator on the left hemi-diaphragm at the level of the spleen.

Series 5: Axial T2 navigator-triggered

We have found T2 TSE BLADE/PROPELLER to be qualitatively comparable to, if not favored over, conventional T2 TSE acquisitions, particularly given the reduced sensitivity to cardiac motion and increased sharpness of the major tissue interfaces. Fat saturation is routinely employed for this series. In addition to lesion characterization, this sequence is highly useful for the evaluation of lymphadenopathy and regional bone marrow signal.

Series 6: Axial diffusion-weighted imaging, respiratory-triggered

For this 2D multislice echo planar imaging (EPI) respiratory-triggered acquisition, we have selected b values of 0, 100, and 800 s/mm 2 . Diffusion-weighted imaging (DWI) in other body systems has provided information suggesting the cellularity of the lesion of interest and, because of this, is of particular interest as a potential biomarker of disease and treatment response. To obviate any T2* effects that could be induced in the lesion due to gadolinium, we have decided to perform DWI prior to contrast administration. Further investigation is needed to determine if "pseudoperfusion" (intravoxel incoherent motion) effects elucidated by using lower b-values (less than 100 s/mm 2 ) provide additional clinically relevant information.

Series 7: Pregadolinium T1 3D SPGR

A variety of 3D T1-weighted fat-saturated gradient recalled echo (GRE) sequences are available. Currently, we use a 3D spoiled gradient recalled (SPGR) with accelerated parallel imaging acquisition technique (Siemens VIBE with CAIPIRINHA or GE LAVA-Flex with Auto-calibrating Reconstruction for Cartesian (ARC) sampling and Dixon method for fat suppression, repition time/echo time TR/TE (3.82/1.8 ms), and matrix/slice thickness (256 × 256)/3 mm. In- and -out-of-phase images are routinely reconstructed. Homogeneous fat saturation of the anterior-superior mediastinum near the origin of the great vessels can be challenging with non-Dixon methods and particular attention to manual shim boxes is helpful in this regard.

Series 8: Test bolus

For this portion, repeated real-time single-slice GRE axial acquisitions at the level of the pulmonary artery are acquired following injection of 1 cc of intravenous contrast followed by a 20 cc normal saline flush. The time to peak enhancement in the pulmonary artery or ascending aorta can be determined.

Series 9: Postgadolinium T1 3D SPGR

Using the information from the test bolus, the initial postgadolinium series is timed such that peak arterial enhancement coincides with the time of central k-space filling. Identical parameters are used for the pre- and postgadolinium series, with images typically acquired in the axial plane. Subsequent postgadolinium images are typically obtained at 1, 3, and around 5 min. An additional imaging plane, either coronal or sagittal, is often obtained.

Series 10 (optional): T1 SPGR breath-held In- and out-of-phase

The information provided by this dual-echo 2D GRE sequence with respect to the presence of intravoxel fat is particularly useful in imaging anterior mediastinal masses where the normal or hyperplastic thymus is a consideration. [10] The imaging parameters are Repetition Time/First Echo Time/Second Echo Time (TR/TEΉ/TE΂) (170/2.38/4.76 ms), matrix/slice thickness (256 × 192)/5.5 mm. In practice, we have found the in- and out-of-phase images obtained from the pregadolinium T1 3D SPGR with Dixon technique can be comparably used, thus saving the time associated with running a separate two-dimensional T1-weighted Gradient-Recalled Echo (2D T1 GRE) for this purpose.

Series 11 (optional): Axial bSSFP breath-held

The 2D bSSFP (Siemens TRUE FISP or GE FIESTA) technique demonstrates T2/T1-weighting with high contrast and signal-to-noise ratio and can be obtained with rapid sequential acquisition, fat suppression, and overlapping thin sections. It is frequently used in cardiac and abdominopelvic MRI as a noncontrast-enhanced bright blood MR angiography/venography technique. These are typically performed as breath-held acquisitions but can be tailored to be free-breathing.

Series 12 (optional): Cine bSSFP

CinebSSFP (Siemens TRUE FISP or GE FIESTA) is a staple of cardiac imaging for the evaluation of cardiac wall motion, function, and valves. In the context of noncardiac chest MRI, this technique is useful for evaluating the motion of an intrapulmonary mass relative to the mediastinum or chest wall in assessing for possible invasion.

We have found that the above sequences and modifications provide a robust set of tools to draw upon in answering most clinical questions. As always, a specific examination may require additional considerations, such as ECG-gating or an angiographic technique. It is becoming increasingly common for facilities to have default protocols and radiologists sitting in the reading room at a remote site. We believe it is important for the radiologist to evaluate the quality of the scan while the patient is still on the scanner as there are several opportunities to optimize or shorten the scan right at the console. Shortening the scan time can be particularly important for patients who are dyspneic, anxious, or who have trouble lying supine for a prolonged time, all fairly common occurrences in our patient population.

PULSATILE TINNITUS MRI protocol



SAGITTAL T1
AXIAL T2
AXIAL FLAIR
AXIAL PRE T1
AXIAL  T1 POST FS
CORONAL T1 POST FS
MRA COW POST CONTRAST

PATIENT
COIL TYPE
HEAD
HEAD
HEAD
HEAD
HEAD
HEAD
HEAD

POSITION
PLANE
SAGITTAL
AXIAL
AXIAL
AXIAL
AXIAL
CORONAL
AXIAL

PARAMETERS
MODE
2D
2D
2D
2D
2D
2D
3D


PULSE SEQUENCE
FSE
FSE

FSE
FSE
FSE
FL

USER CV’S
PSD








SCAN TIMING
FLIP ANGLE






30


TE
MIN-FULL
85
130
MIN #
MIN #
MIN #
4


TR
400-800
3000-6000
9000
350-800
350-800
350-800
35


TI


2200






AUTO CF
WATER
WATER
WATER
WATER
WATER
WATER



FLOW DIRECTION

SLICE
SLICE





SCANNING RANGE
FOV
21-24
20
20
16
16
16
21


SLICE THINKNESS
5/0
5/0
5/0
3/0
3/0
3/0
0.8


# SLICES
AS NEEDED
28
28



SLAB


SAT
I
I
I
16
16
16


AT THIS LEAST AMOUNT
MATRIX
256X192
256X256
256X192
3/0
3/0
3/0
256X192


FREQ DIRECTION
S/I
A/P
A/P
A/P
A/P

A/P

COMMENTS

COVER ENTIRE BRAIN
WHOLE BRAIN
WHOLE BRAIN
IAC ONLY
IAC ONLY
IAC ONLY
CUT OUTS INCLUDE ALL THE VESSELS

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