ASNC imaging guidelines/SNMMI procedure standard for positron emission tomography (PET) nuclear cardiology procedures
ASNC imaging guidelines/SNMMI procedure standard for positron emission tomography (PET) nuclear cardiology procedures
Vasken Dilsizian 5
Stephen L. Bacharach 3
Rob S. Beanlands 4
Steven R. Bergmann 1
Dominique Delbeke 2
Sharmila Dorbala 0
Robert J. Gropler
g Juhani Knuuti
h Heinrich R. Schelbert
Mark I. Travin
0 Division of Nuclear Medicine, Brigham and Women's Hospital , Boston, MA
1 Pat and Jim Calhoun Cardiology Center, UConn Health , Farmington, CT
2 Department of Radiology, Vanderbilt University Medical Center , Nashville, TN
3 Department of Radiology, University of California-San Francisco , San Francisco, CA
4 Division of Cardiology, University of Ottawa Heart Institute , Ottawa , Canada
5 Department of Diagnostic Radiology and Nuclear Medicine, University of Maryland School of Medicine , Baltimore, MD
Stress-induced myocardial perfusion defects have
been firmly established as an important diagnostic and
prognostic technique for identifying flow-limiting
epicardial coronary artery disease (CAD). However,
interpretation of such myocardial perfusion imaging
(MPI) studies has been primarily qualitative or
semiquantitative in nature, assessing regional perfusion
defects in relative terms. Quantitative positron emission
tomography (PET) measurements of myocardial blood
flow (MBF) in absolute terms (milliliters per gram per
minute) offer a paradigm shift in the evaluation and
management of patients with CAD. The latter is
concurrent with the recent shift in the management of CAD
from an anatomical gold standard (i.e., coronary
angiogram) to a functional one. Moreover, non-invasive
quantification of MBF extends the scope of conventional
MPI from detection of end-stage, advanced, and
flowlimiting epicardial CAD to early stages of
atherosclerosis or microvascular dysfunction and assessment of
balanced reduction of MBF in all three major coronary
arteries. Quantitative approaches that measure MBF
with PET identify multivessel CAD and offer the
opportunity to monitor responses to lifestyle and/or risk
factor modification and to therapeutic interventions.
PET utilizes radionuclide tracer techniques to
produce images of in vivo radionuclide distribution using
an external detector system. Similar to computed
tomography (CT), the images acquired with PET
represent cross-sectional slices through the heart. However,
with PET, the image intensity reflects organ function
and physiology as opposed to anatomy. The functional
information that can be obtained from PET images
depends upon the radiopharmaceutical employed. PET
allows non-invasive evaluation of MBF, function, and
metabolism using physiological substrates prepared with
positron-emitting radionuclides, such as carbon, oxygen,
nitrogen, and fluorine. These radionuclides have
halflives that are often considerably shorter than those used
in single photon emission computed tomography
(SPECT). Positron-emitting radionuclides can be
produced using a cyclotron (e.g., 18F-fluoro-2-deoxyglucose
[18F-FDG] with a 110-minute half-life) or using a
generator (e.g., rubidium-82 [82Rb] with a 75-second
half-life from a strontium-82 [82Sr] generator).
PET radionuclides reach a more stable configuration
by the emission of a positron. Positrons are the
antimatter of electrons. They are positively charged particles
with the same rest mass as electrons. When a positron
spends time near an electron, the two annihilate—they
both disappear and in their place two 511-keV gamma
rays are emitted. Because the gamma rays are nearly
collinear (discharged at 180 to each other) and travel in
opposite directions, the PET detectors can be
programmed to register only events with temporal
coincidence of photons that strike directly at opposing
detectors.1 The result is improved spatial (4- to 6-mm)
resolution when compared with SPECT, as well as
temporal resolution. The high temporal resolution of
PET is also explained by the fact that the imaging device
is stationary compared with the rotating imaging gantry
for SPECT. Moreover, the PET system is more sensitive
than a SPECT system due to the higher count rate and
provides the possibility of attenuation correction. The
result of these advantages with PET is the potential for
quantitation of tracer concentration in absolute units.
Quantification of MBF may provide diagnostic and
prognostic information earlier than visual interpretation
of relative radiotracer uptake, which is a fundamental
disadvantage of the conventional SPECT technique.
The PET detectors are placed in a ring, surrounding
the patient, and are configured to register only photon
pairs that strike opposing detectors at approximately the
same time, termed coincidence detection. Over the
course of a typical scan, millions of coincidence events
are recorded, and projections of the activity distribution
are measured at all angles around the patient. These
projections are subsequently used to reconstruct an
image of the in vivo radionuclide distribution using the
same algorithms as those used in SPECT and x-ray CT.
The resulting PET images have improved spatial and
temporal resolution when compared to SPECT. Hence,
the imaging properties of PET meet some of the Centers
for Medicare & Medicaid Services (CMS)
implementation of quality initiatives to assure quality health care.
PET MPI is effective (high diagnostic accuracy), safe
(low radiation exposure), efficient (short image
acquisition times), and patient-centered (accommodates ill or
higher risk patients, as well as those with large body
habitus), providing equitable and timely care.
Recent advances in hybrid PET/CT instrumentation
and multichannel spiral CT allow detailed, non-invasive
visualization of the coronary arteries, as an adjunct to
PET imaging. Whereas multichannel CT angiography
provides information on the presence and extent of
anatomical luminal narrowing of epicardial coronary
arteries, stress myocardial perfusion PET provides
information on the downstream functional consequences
of such anatomic lesions. Thus, with hybrid PET/CT
systems, complementary information of anatomy and
physiology can be obtained during the same imaging
session. The ability to evaluate CAD, myocardial
perfusion, metabolic viability, and ventricular function
from a hybrid PET/CT image makes such systems an
important tool in the clinical practice of cardiology.
In the last few years, not only have combined PET/
CT scanners proliferated, but PET combined with
magnetic resonance (MR) imaging scanners have been
introduced (PET/MR). While the main use for these
scanners continues to be for oncological applications,
cardiac CT and MR are now well established. The
melding of CT or MR to a PET camera increases the
complexity of scanning protocols, quality maintenance
and assurance but also expands imaging to correlate
anatomy, molecular biology, and metabolism with
nuclear imaging thereby providing comprehensive
evaluation of the heart. For example, co-registration of
18FFDG metabolic imaging with morphological, functional,
and tissue imaging attributes of MR presents new
opportunities for disease characterization, such as
cardiac sarcoidosis, hallmarked by inflammatory injury,
non-caseating granuloma formation, and organ
dysfunction which could be the first clinical application of PET/
MR in cardiology.2 18F-FDG PET in cardiac sarcoidosis
produces ‘‘hot spot’’ images. MR is particularly helpful
for anatomic co-localization of the 18F-FDG PET signal
within the heart, reflecting the inflammatory phase of
cardiac sarcoidosis. MR delayed enhancement, on the
other hand, provides information on areas of fibrosis and
scar as a consequence of cardiac sarcoidosis. It is
reasonable, therefore, to have a hybrid system in which
MR can show the focus of prior injury or scar from
sarcoidosis superimposed on inflammatory markers seen
The current document is an update of an earlier
version of PET guidelines that was developed by the
American Society of Nuclear Cardiology (ASNC).4 The
publication is designed to provide imaging guidelines for
physicians and technologists who are qualified to
practice nuclear cardiology. While the information supplied
in this document has been carefully reviewed by experts
in the field, the document should not be considered
medical advice or a professional service. We are
cognizant that PET, PET/CT, and PET/MR technology is
evolving rapidly and that these recommendations may
need further revision in the near future. Hence, the
imaging guidelines described in this publication should
not be used in clinical studies until they have been
reviewed and approved by qualified physicians and
technologists from their own particular institutions.
PET, PET/CT, AND PET/MR INSTRUMENTATION
PET Imaging Systems
The majority of dedicated PET cameras consist of
rings of small detectors that are typically a few
millimeters on a side, and tens of millimeters deep.
Coincidences between detectors in a single ring produce
one tomographic slice of data. Usually, one or more
adjacent rings may also contribute to counts in that slice.
In a 2-dimensional (2D) or ‘‘septa-in’’ PET scanner,
there is a septum (e.g., lead or tungsten) between
adjacent rings. This septum partially shields
coincidences from occurring between detectors in one ring and
detectors in a non-adjacent or more distant ring. By
minimizing coincidences between a ring and its more
distant neighboring rings, the septa greatly reduce
A scanner with no septa in place is referred to as a
3-dimensional (3D) or ‘‘septa-out’’ scanner. This
nomenclature is somewhat confusing as both septa-in
and septa-out modes produce 3D images. The septa-out
(3D) mode, however, permits coincidences between all
possible rings, greatly increasing sensitivity but also
greatly increasing scatter, as well as the count rate for
each individual detector. This increase in count rate can
increase dead time and random events. The increased
sensitivity is the greatest for the central slice and falls
rapidly and roughly linearly, for slices more distant from
the central slice. The slices near the edge have a
sensitivity about the same as in a 2D scanner but with
greater scatter. Scatter is measured with standards
provided by the National Electrical Manufacturers
Association (NEMA)5–9 and is typically in the order of
10 to 15% for 2D scanners and 30-40% or more for 3D
scanners. In chest slices encompassing the heart, as
opposed to the relatively small NEMA phantom, there is
an even larger increase in scattered counts for 3D
imaging. For cardiac applications, scatter tends to
artifactually increase the counts in cold areas surrounded
by higher activity regions (e.g., a defect surrounded by
normal uptake, or near the liver).
Some scanners have retractable septa, permitting
the user to choose between 2D and 3D operation. Many
PET/CT manufacturers have opted for scanners that
operate only in 3D mode, because these allow maximum
patient throughput for multi-bed position oncology
studies. Situations in which 3D mode may be
advantageous include the following:
1. Whole-body patient throughput is important (e.g., a busy oncology practice).
2. Radiation exposure is critical, so that reductions in injected activity are desired.
3. Special (i.e., usually research) radiopharmaceuticals
are being used, which can only be produced in
As noted above, although 3D acquisition is in principle
many times more sensitive than 2D, ‘‘accidental,’’ or
random coincidences (termed randoms), dead time, and
scatter can greatly reduce the effective sensitivity of images
acquired in 3D, especially at high doses. Thus, in order to
prevent poor-quality images, lower doses are often
administered in 3D mode. Accordingly, 3D imaging can be used
when the dose must be minimized (e.g., in normal
volunteers, in children, or when multiple studies are
planned) or when scatter is minimal (e.g., brain imaging).
The advent of lutetium-based crystals, such as lutetium
oxyorthosilicate (LSO) and lutetium yttrium orthosilicate
(LYSO) along with gadolinium oxyorthosilicate
(GSO)based PET scanners, and even bismuth germanate (BGO)
scanners with new-generation optimized photomultiplier/
crystal coupling schemes and high-speed electronics, has
made 3D imaging more practical. Improvements in
software, coupled with improvements in electronics and crystal
technology, can, in part, compensate for the increase in
randoms, dead time, and scattered events associated with
3D imaging.10 The use of 3D-cardiac imaging with
newgeneration machines continues to be evaluated. The degree
to which any of these improvements in 3D is achieved in
practice for cardiac imaging may vary between
manufacturers and between applications (high-count rate versus
normal count rate studies).
PET Imaging: Crystal Types
Three different crystal types are commonly
employed in PET, including BGO, GSO, and
lutetiumbased crystals, such as LSO and LYSO, although other
crystal types have also been used. The technical
specifications of each crystal type have been well
documented.11 Each type of crystal has been used
successfully for cardiac imaging. BGO has the highest
stopping power, but relatively poor energy resolution
(which limits energy-based scatter reduction) and poor
timing resolution (limiting its ability to reduce randoms
at high count rates). GSO, LSO, and LYSO have better
timing resolution and, in theory, better energy
resolution. For 2D imaging, GSO, LSO, and LYSO may not
offer significant advantages over BGO, given the
inherently high sensitivity of BGO and the lower count rates
encountered in 2D versus 3D studies. The main
advantage of the GSO and lutetium-based crystals is reduced
dead time, which enables them to acquire data at higher
count rates associated with operating in 3D mode, and to
better minimize the effects of randoms. One minor
disadvantage of LSO and LYSO is their intrinsic
radioactivity, which contributes to a small increase in
the random event rate.
The better energy resolution of GSO, LSO, or
LYSO compared to BGO, and consequent reduction of
scatter, would in principal make these detector types
advantageous in 3D mode. At present, the theoretical
energy resolution for these detectors does not seem to
have been fully realized in practice, leaving all four
crystal types with similar energy-based scatter rejection
(i.e., GSO and lutetium-based crystals giving an
improvement, but not a great one, over BGO) and
making 2D imaging still the method of choice if scatter
rejection is critical.
Modern image reconstruction algorithms
incorporate improved models for scatter correction, and as a
result, the impact of scatter for state-of-the-art scanners
operating in 3D mode is usually acceptable for clinical
imaging. In cardiac imaging, areas of low uptake (e.g.,
perfusion defects) may still be slightly overestimated
with 3D compared to 2D when these defects are near
regions of high tracer uptake. The suitability of 3D mode
for cardiac PET imaging should be evaluated by the
user. For studies with a wide range of count rates, such
as quantitative 82Rb scans, 3D acquisitions can be
problematic unless great care is taken to address the high
count rates achieved during and immediately after
infusion. Therefore, for 3D 82Rb acquisitions, GSO
and lutetium-based crystals are thought to have an
advantage over BGO. Improvements in crystal
manufacture and design, as well as the development of
scanners with new crystal types, may further improve
3D scatter rejection and 3D imaging during bolus
injections (e.g., quantitative 82Rb studies).
PET Time-of-Flight (TOF) Imaging
Machines that incorporate time-of-flight (TOF)
information in the acquisition process have been
developed and are available. TOF refers to the time difference
between when the two 511-keV annihilation photons
reach their respective detectors, 180 apart. For
example, if the positron annihilation occurred at the center of
the machine, the two photons would reach their
respective detectors at exactly the same time, while if the
annihilation occurred closer to one detector than the
other, the photon would reach the closer detector first. If
the time difference could be measured accurately
enough, it would be possible to determine exactly where
the annihilation event is originated.
Unfortunately, current detector and instrumentation
technology is not nearly good enough to achieve this
level of accuracy. However, it has been shown that
adding TOF capability can improve the statistical
quality of the data (i.e., the noise).12–14 For example,
recent reports indicate that TOF imaging can improve
noise and image quality in 13N-ammonia perfusion
imaging,15 and therefore potentially improve image
quality or even perhaps, in the future, reduce the dose
needed to achieve a given image quality. In addition, as
mentioned above, performing high-count rate cardiac
studies with 3D scanners presents difficulties.
Preliminary studies indicate that some of these difficulties may
be reduced with TOF imaging; however, much work
remains to be done. As most users do not use machines
in the TOF mode, quality control (QC) of this feature
should follow recommendations of the manufacturer and
NEMA NU 2-2012 testing procedures.5
Hybrid PET/CT and PET/MR Cameras
For many years, most PET scanners have been sold
combined with a CT scanner. In all cases, the
manufacturer starts with a state-of-the-art PET scanner, whose
characteristics have been described in the section above.
The manufacturer then adds a CT system, with 64 or
more slices. These combined systems, in practice,
demonstrate a range of integration. At one end of the
spectrum, the hardware and software of the CT systems
are completely integrated within the PET scanner. A
common, unified gantry is used and a single, unified
software system with an integrated PET/CT interface is
provided. At the other end of the spectrum, the hardware
and software of the CT system are less integrated. In
some machines, a separate CT gantry is carefully placed
in front of or behind the PET gantry, and a separate
workstation is used to control the CT system. Although
originally the CT component of the hybrid PET/CT
camera was developed for attenuation correction and
anatomical co-localization purposes, more modern
machines have CT scanners that are of diagnostic
quality, which allows the assessment of both coronary
artery calcium scoring and CT angiography. The scope
of these CT procedures is beyond the purview of these
PET guidelines, and has been covered in a recent
SNMMI/ASNC/SCCT guideline.16 More recently, PET
scanners have also been introduced combined with MR.
Two different types of systems are available—in-line
systems and simultaneous systems. The first uses a
common gantry for both imaging modalities, and is very
similar to PET/CT devices with the CT replaced by MR.
In-line systems allow existing state-of-the-art PET and
MR scanners to be combined adjacently, although
alterations may be necessary to accommodate the nearby
high magnetic fields. The so-called ‘‘simultaneous’’
systems allow both image sets to be acquired at the same
time—although depending on their design there may be
some performance limitations. Attenuation correction
with either type of system can be problematic. Unlike
CT images, MR images do not necessarily produce
images from which PET attenuation correction factors
can be derived. MR imaging is, of course, quite valuable
in cardiology, so it is possible that the combination of
MR with PET will result in interesting new clinical
applications. PET/MR is still in its early stages and
much work remains before its full clinical potential in
cardiology is recognized.
PET Imaging: Attenuation Correction
For dedicated PET scanners (without CT or MR),
rotating rod sources or rings of germanium-68
(68Ge)/gallium-68 (68Ga) or cesium-137 (137Cs) are
used to acquire a transmission scan for attenuation
correction. A typical transmission scan with rotating
rods adds about 60 to 600 seconds to the overall
imaging time. This is acceptable for cardiac imaging,
but is a significant drawback for multi-bed position
oncology scans. Because oncology applications
continue to drive sales of PET scanners, manufacturers
looked for a way to reduce this transmission scan time.
For this reason, and because of other advantages of CT,
nearly all current commercially available PET scanners
are hybrid PET/CT systems. These scanners, in
general, have eliminated the rotating rod source and
instead rely on CT scans for attenuation correction.
The Hounsfield units (HU) generated by the CT
scanner can usually be accurately converted into PET
CT-based attenuation correction typically adds less
than 10 seconds to the cardiac scan time. The use of
either CT or the rotating rod for attenuation correction
requires precise alignment between the transmission
image and the emission image. An advantage of CT over
transmission sources is a much reduced scan time, which
helps reduce overall patient motion. The high speed of
CT scans, however, freezes the heart and lungs at one
phase of the respiratory cycle, causing potential
misalignment between the CT-based transmission and
emission scans. The latter, of course, are averaged over
many respiratory cycles. The respiratory misalignment
between the CT image and emission data can produce
significant artifacts and errors in apparent uptake in the
myocardial segments adjacent to lung tissue.17 Errors in
attenuation correction from misregistration are typically
much worse if the CT is acquired at full inspiration, and
so the CT is often acquired at either end-expiration or
during shallow breathing. Software realignment must be
performed to minimize any remaining misalignment.
Other techniques (e.g., slow CT, respiratory gating, and
4D-CT) are under development for compensating for
respiratory motion, but are still in the research phase and
are not further described here.
MR images, unlike CT or rotating rod images, do
not directly measure attenuation values. Instead,
MRbased attenuation correction usually must rely on
indirect methods, for example using the MR image to
separate tissue types (e.g., lung, soft tissue, and bone).
The segmented images are then used to assign each
tissue type a pre-determined attenuation value. Use of
this method for organs, such as the heart, with a tissue/
lung interface, still requires further study.
PET AND PET/CT OR PET/MR IMAGING QC
PET QC Procedures
The procedures below should be suitable for
ensuring overall proper basic operation of a PET scanner.
Table 1 lists the recommended PET imaging QC
schedules.4 Note that, unlike planar and SPECT
imaging, there are no widely accepted, published QC
procedures for PET. Some additional procedures may
be required by particular manufacturers.
Acceptance testing. It is recommended that the
NEMA performance measurements, as defined by NU
22012,5 be made before accepting the PET scanner. Many
of these tests can be performed by the company
supplying the PET scanner. If so, it is recommended
that the purchaser’s representatives work with the
manufacturer’s representatives during these tests. The
NU 2-2012 recommendations have superseded the NU
2-2007 recommendations.8 In scope, the tests are nearly
equivalent between NU 2-2012 and NU 2-2007.5,8 For
cardiac imaging, these QC performance standards
should be performed.
There are two reasons for making these
1. To ensure the new PET scanner meets specifications published by the manufacturer and
2. To provide a standard set of measurements that allows the user to document the limitations of the scanner and to provide a standard against which to track changes that may occur over time.
Daily QC scan. Each day the PET detectors
should be evaluated to ensure proper operation before
commencing with patient injections or scans. The daily
quality procedure varies according to the design of the
scanner and recommendations of the vendor. For
example, some scanners use an attenuation blank scan to
evaluate detector constancy, and others may use a scan
of a standard phantom. In addition to numerical output
of the scanners (chi-square, uniformity, etc.), the raw
sinogram data also should be inspected to evaluate
Sensitivity. NEMA NU 2-2012 provides
recommended procedures for measuring system sensitivity.5
Subtle changes in PET system sensitivity may occur
slowly over time. More dramatic changes in sensitivity
may reflect hardware or software malfunction. There are
simple tests designed to monitor such changes in
sensitivity. Ideally, these tests should be performed
weekly, but no less than monthly. For many systems, the
daily QC scan also provides a measure useful for
tracking changes in sensitivity.
Spatial resolution. Spatial resolution is
measured using a point source as specified in the NEMA NU
Scatter fraction. Intrinsic scatter fraction is
measured according to NEMA NU 2-2012
Accuracy of attenuation correction and
overall clinical image quality. Attenuation
correction should be assessed using the IEC phantom, as
specified in the NU 2012 recommendations.5 If this
phantom is not readily available, it is suggested that
similar measurements be performed with a phantom
approximating a typical human body shape and size
(e.g., a 20- by 30-cm elliptical phantom or
anthropomorphic phantom). It should have at least one cold
sphere or cylinder and one hot sphere or cylinder, as
well as some material simulating lung tissue to ensure
proper performance in the presence of non-uniform
Variations among manufacturers. The
above recommendations regarding PET scanner quality
assurance are general guidelines. In addition, each
manufacturer has its own periodic QC recommendations
for parameters such as ‘‘singles’’ sensitivity,
coincidence timing, energy calibration, and overall system
performance. These, by necessity, require different
measurement protocols that may vary even between
models for the same manufacturer. These measurements
must be performed as detailed by the manufacturer.
However, the measurements specified above are not
intended to replace these basic system-specific QC
CT QC Procedures
The procedures below should be suitable for
ensuring overall proper basic operation of a CT scanner.
Table 2 lists recommended CT imaging QC schedules.
Some additional procedures may be required by
Calibration. The reconstructed CT image must
exhibit accurate, absolute CT numbers in HU. This is
critical for the use of CT images for PET attenuation
correction, because the quantitative CT values are
transformed, usually via a bilinear or trilinear function
with one hinge at or near the CT value for water, to
attenuation coefficients at 511 keV. Any errors in CT
numbers will be propagated as errors in estimated
511keV attenuation coefficients, which in turn will
adversely affect the attenuation-corrected PET values.
CT system calibration is performed with a special
calibration phantom that includes inserts of known CT
numbers. This calibration is done by the manufacturer’s
field-service engineers. The CT calibration is then
checked daily with a water-filled cylinder, usually 24
cm in diameter provided by the manufacturer. In
practice, if the error is greater than 5 HU (i.e., different
than the anticipated value of 0 HU), the CT system is
considered to be out of calibration. The technologist will
then usually perform an air calibration, to determine if
this corrects the overall calibration (i.e., brings the CT
number for water back to within 5 HU of 0). If it does
not, the manufacturer’s field-service engineer must be
called. On an annual basis, or after any major repair or
calibration, calibration is checked by the manufacturer’s
Field uniformity. The reconstructed CT image
must exhibit uniform response throughout the field of
view (FOV). In practice, this means a reconstructed
image or a uniform water-filled cylinder must
demonstrate low variation in CT number throughout this
image. In practice, small circular regions of interest
(ROIs) are placed at the four corners of the cylinder
image, and the mean CT number is compared to that
from a region in the center of the phantom; the
difference in mean region CT number should not exceed
5 HU. Non-uniformities greater than this may produce
sufficient quantitative inaccuracies so as to affect PET
attenuation correction based on the CT image.
Table 3 lists recommended CT QC schedules for
combined PET/CT units. Users should consult the
manufacturer regarding the specific manner and
frequency with which tests should be performed for the CT
component of their PET/CT device. Both the American
College of Radiology (ACR) and American Association
of Physicists in Medicine (AAPM) have published CT
testing procedural guidelines.18
Combined PET/CT QC Procedures
The PET and CT portions of the combined system
should be assessed as described for the dedicated PET
and CT imaging devices. In addition to the independent
QC tests for the PET and CT portions of the combined
system, it is necessary to perform additional tests that
assess the combined use of PET and CT. Table 4 lists
recommended QC procedures for combined PET/CT
Registration. The reconstructed PET and CT
images must accurately reflect the same 3D locations
(i.e., the two images must be in registration). Such
registration is often difficult because the PET and CT
portions of all commercial combined PET/CT systems
are not coincident (i.e., the PET and CT ‘‘slices’’ are not
in the same plane) and the PET and CT gantries are
contiguous. In practice, this means that the PET and CT
acquisitions do not simultaneously image the same slice.
In fact, because the bed must travel different distances
into the gantry to image the same slice in the patient for
PET versus CT, there is ample opportunity for
misregistration via x, y, z misalignment of bed motion—or, of
perhaps even greater concern, because of differential
‘‘bed sag’’ for the PET and CT portions, depending on
the table design.
In addition, electronic drift can influence the
‘‘position’’ of each image, so that calibrations for
mechanical registration can become inaccurate over
time. Thus, it is imperative to check PET-to-CT
registration on an ongoing basis. This is usually performed
with a specific phantom or jig containing an array of
point sources visible in both PET and CT. Errors in
colocation in the fused PET/CT images are assessed, such
as by means of count profiles generated across transaxial
slices. Such errors, after software registration
corrections, should be less than 1 mm. It is important to image
this registration jig in a number of positions along the
bed. It may also be helpful to place a weight on the end
of the bed to produce some bed sag and repeat the
assessment. The above considerations are in addition to
the patient-specific alignment QC clinically necessary to
assess possible patient or respiratory motion.
Attenuation correction accuracy. The use of
the CT image for PET attenuation correction requires a
transformation of the observed CT numbers in HU to
attenuation coefficients at 511 keV. This transformation
is usually accomplished with a bilinear or trilinear
calibration curve, with one ‘‘hinge’’ at a CT value of 0
(i.e., hinged at the CT value for water).
At a minimum, it is important to image a water-filled
cylinder to assess PET field uniformity and PET activity
concentrations after CT-based PET attenuation
correction. Errors in CT-to-PET attenuation transformations are
usually manifest as a corrected PET image without a
‘‘flat’’ profile from edge to center (i.e., the activity at the
edge is either too high or too low relative to that at the
center of the phantom) and with resulting
attenuationcorrected absolute PET values that are incorrect (although
these values depend on absolute PET scanner calibration
as well as accurate CT-based PET attenuation correction).
If possible, the CT-based attenuation-corrected PET
values should be compared with those from the rotating
rod source-based attenuation-corrected PET values in the
same phantom. Moreover, if available, more sophisticated
phantoms with variable attenuation and variable activity
distributions can be used to more comprehensively assess
any errors in CT-based PET attenuation correction.
The accuracy of CT attenuation-corrected PET
images is still under investigation. Recent work has
reported that even after correcting for potential PET/CT
misalignment, tracer uptake maps derived from
CTbased attenuation correction differ from those derived
using transmission source correction.17,19,20
PET-MR QC Procedure
Many of the principles outlined above for PET/CT
apply to hybrid PET/MR systems. Co-localization is
especially important. Errors in misregistration of CT or
MR and PET emission images can result in significant
reconstruction errors. Because these scanners are still in
evolution, QC from the manufacturer should be
PET ACQUISITION AND PROCESSING
The acquisition and processing parameters defined
in this section apply to both the perfusion and metabolic
PET tracers in the sections that follow.
Ideally, the patient should be placed in the supine
position, with the arms out of the camera’s FOV.
Nearly all patients can tolerate this position, provided
that some care is given to a method to support the
arms. Alternatively, an overhead bar has often been
used as a handhold for arm support. In patients with
severe arthritis, whose arms cannot be positioned
outside the camera’s FOV, cardiac images should be
obtained with the patient’s arms resting on his/her
side. In the latter case, the transmission scan time may
have to be increased, and it is of critical importance
that the arms not move between the transmission and
emission scans, or artifacts will result. When
performing perfusion/metabolism PET studies, it is imperative
to keep the patient positioned similarly for both
studies. In patients undergoing PET/CT imaging, arms
resting inside the FOV will result in beam-hardening
artifacts on the CT-based transmission scan, which
usually lead to streak artifacts on the corrected
In determining appropriate patient doses, the
following issues should be considered:
1. Staff exposure could be high because of the limited
effectiveness of shielding and the potential for large
doses (e.g., 82Rb PET). Thus, standing in close
proximity to an 82Rb generator or the patient during
injection should be avoided. It is also important to
point out that a lead apron is not helpful in shielding
the 511-keV photons. In fact, it may increase staff
exposure due to secondary electrons emitted from the
511-keV photon interaction with lead.
2. Large patients may benefit from higher doses. 3. 3D imaging requires less dosage than 2D imaging due to the improved sensitivity of the system. Total Counts
The counts per slice necessary to yield adequate
quality images will vary from camera to camera
depending, in part, on scatter and randoms corrections,
as well as the amount of smoothing that is performed. If
one tries to achieve on the order of 7 mm full width at
half maximum (FWHM) in-plane resolution and has 10
to 15% scatter, then a typical good-quality study in 2D
mode might have on the order of 50,000 true counts per
millimeter of transaxial distance over the region of the
heart (e.g., for a 4.25-mm slice separation, the number of
counts would be 50,000 9 4.25 = 250,000 counts per
slice). These numbers are approximate and may differ
from one scanner to the other. If one is willing to accept
a lower resolution (e.g., more smoothing) or more noise,
imaging time can be reduced. 3D scanners have greater
scatter, and therefore they usually require more counts
than a 2D scanner to achieve the same noise level.
It is recommended that 2–3 mm/pixel be used. A
rule of thumb in nuclear medicine physics is that one
should have at least 3 pixels for every FWHM of
resolution in the image. For example, if the data are
reconstructed to 8 mm FWHM, then this corresponds to
roughly 8 mm/3 = 2.7 mm/pixel. Many institutions
achieve a 3 mm sampling rate or better with a 256 9 256
array over the entire FOV of the camera. Other
institutions choose to use a 128 9 128 array over a
limited FOV (e.g., 25 to 35 cm diameter) centered over
the heart, in which case, 2 to 3 mm/pixel is easy to
achieve, cutting out extraneous structures in the FOV,
even with a 128 9 128 array. Either method is
acceptable to achieve the desired 2 to 3 mm/pixel.
Greater than 3 mm/pixel may be acceptable for older
PET cameras with resolution worse than 1 cm FWHM.
Imaging Mode (Static, Gated, or Dynamic)
Static PET acquisition produces images that allow
relative assessment of tracer uptake on a regional basis.
Comparison of regional tracer uptake in relation to the
normal tracer distribution is the current standard for the
identification of regional abnormalities. However, given
the growing literature regarding the incremental value of
absolute MBF measurement to the visual interpretation
of relative radiotracer uptake, it is strongly
recommended that the data be acquired in dynamic mode (i.e.,
binning the data with time).
Usually, PET tracer counts are sufficiently high to
yield a good-quality ventricular function study.
Electrocardiographic (ECG)-gated images are acquired in 8 to
16 time frames per R-to-R interval, in a manner similar
to SPECT-gated perfusion studies but at higher spatial
resolution. Given that ventricular contraction and
thickening are often clinically useful for assessing viability,
gating should be performed when possible. It is
important that the gating software does not adversely affect
the ungated images (e.g., by loss of counts as a result of
beat length rejection). Monitoring the length and number
of the accepted beats is critical to assure the accuracy of
the gated data. Arrhythmias, such as atrial fibrillation,
frequent premature ventricular contractions (PVCs), or
other abnormal rhythms can lead to highly erroneous
gated information. List-mode acquisition may obviate
most of these problems.
For a dynamic acquisition, PET data are acquired in
multiple time-sequenced frames. A potential advantage
of the dynamic over static acquisition is patient motion
artifact. For example, if a patient should move at the end
of the study, select and utilize only those dynamic
frames with no motion (i.e., summing them together to
make one static image). This is easily implemented and
takes almost no additional operator time. A more
elaborate dynamic acquisition beginning just prior to
the bolus injection of the tracer may be used optionally
when kinetic analysis is to be performed (e.g.,
compartmental analysis or Patlak analysis). Kinetic analysis,
which typically requires only the initial 3 to 5 minutes of
data acquisition, permits absolute quantification of the
tracer’s kinetic properties (e.g., blood flow for 82Rb and
13N-ammonia, rate of 18F-FDG utilization).
Interpretation of quantitative MBF (or metabolic) data requires
appropriate training and expertise beyond that necessary
for visual inspection of static, summed images.
List-mode acquisitions are now available with
nearly all cameras, which enable simultaneous dynamic
and ECG-gated acquisitions. It is the optional
acquisition mode, and is routinely used with many vendors’
data processing software.
Several corrections are required for creating datasets
that can be used for reconstruction. PET data must be
corrected for randoms, scatter, dead time, attenuation,
and decay before reconstruction can begin. Once these
corrections are applied, the data can be reconstructed
with either filtered backprojection (FBP) or iterative
algorithms. FBP is the standard method used for
reconstruction on older PET systems. FBP images are subject
to streak artifacts, especially when the subject is obese or
large. This can affect visual analysis but usually does not
adversely affect quantitative analysis with regions of
interest (i.e., the streaks tend to average out properly over
typical volumes of interest). Newer PET systems employ
iterative reconstruction methods (such as ordered subset
expectation maximization [OSEM]) yielding images
with superior noise properties. Although high-uptake
structures, such as the heart, may not improve their noise
characteristics with iterative reconstruction approaches,
the surrounding lower uptake structures do improve, and
streak artifacts are nearly eliminated, thus greatly
improving the visual appearance of the image. However,
low-uptake areas, such as myocardial defects and the left
ventricular (LV) cavity at late times, may have slightly or
artificially elevated activity levels unless sufficient
iterations are performed. It is recommended that a cardiac
phantom be used to characterize a PET machine and its
reconstruction algorithm’s behavior.
For rest/stress comparisons, the rest/stress images
must have matched resolution. Filtering is usually
necessary to achieve adequate noise properties. Care
must be taken to match reconstructed resolution when
making pixel-by-pixel comparisons of paired
myocardial perfusion and metabolism data.
Cardiac PET imaging should only be performed with
attenuation correction. Attenuation correction can be
accomplished with a rotating line source or ring in a
dedicated PET system or with CT or MRI in a hybrid system.
For dedicated PET systems, two techniques are
typically used for creating the patient-specific
transmission scans: direct measurement of patient attenuation
with a rotating line source of either 68Ge or 137Cs or
segmentation of patient-specific attenuation maps. The
former are very sensitive to the choice of reconstruction
algorithm and, depending on the reconstruction
algorithm used, could require 60 to 600 seconds acquisition
time to produce a reasonable attenuation map.
Segmentation algorithms are relatively insensitive to noise but
are very dependent on the quality of the program used to
perform the transmission scan segmentation and are
influenced by lung-attenuation inhomogeneity (e.g.,
partial volume effects from the liver).
Transmission scans are typically acquired
sequentially, so it is essential that the patient remains still between
transmission and emission images. Either pre- or
posttransmission scanning is acceptable, providing that the
system’s software can adequately correct for residual
emission activity. Simultaneous acquisition of transmission
and emission scans is not recommended unless the high
count rate and rapidly changing distribution of the emission
tracer can be assured to not adversely affect the
transmission scan. If the transmission scan is performed at the
beginning of the study, attention should be made for
potential misregistration with the emission scans, possibly
due to gradual upward creep of the diaphragm, due to
pressure from visceral fat.21
For PET/CT or PET/MR systems, CT or MR can be
used for acquiring a transmission scan for attenuation
correction. An advantage of this approach is the rapid
acquisition of the transmission scan, which can be
repeated for each imaging session, rest and stress
perfusion studies, as well as for subsequent metabolic
imaging, if necessary. The CT or MR scan can be
reviewed for additional, independent diagnostic
information, such as coronary calcium visualization and other
extra-cardiac anatomic information. To acquire a CT- or
MR-based transmission scan, it is necessary to first
acquire a planar scout acquisition. This scan is used to
measure the axial limits of the full acquisition.
Following this acquisition, the transmission scan is acquired.
The best approach for CT transmission scanning is still
evolving, and therefore this guideline can only suggest
some considerations. Some of the considerations for CT
scanning are as follows (see Table 5):
1. If CT is used for either attenuation correction or
anatomical evaluation, it will have an effect on the
kVp and mAs used in the acquisition. A transmission
scan usually requires only a low CT current, as
opposed to calcium scoring or CT angiography,
which require higher CT currents.
2. Breathing protocols are not fully established. Recent
data suggest that respiratory averaging may be a
useful method of reducing breathing-related artifacts.
Other methods, such as free breathing with a slow CT
scan or ultra-rapid CT acquisition (depending on the
CT device available), have also been proposed.
Current practice discourages breath holding,
particularly in end-inspiration because of the potential for
it to cause uncorrectable misregistration. A CT
transmission scan performed at the same speed, as
for whole-body PET/CT images, frequently produces
artifacts at the lung-liver interface and can sample
parts of the heart and diaphragm in different
positions, causing misregistration and an artifact
where pieces of the diaphragm appear to be
suspended in the lung. Although specifics vary among
laboratories, the duration of the CT transmission scan
is typically from 10 to 30 seconds. CT attenuation
correction with 64-slice devices can achieve an
ultrarapid CT scan in 1.5 seconds, which appears to
reduce such CT artifacts. Therefore, it is imperative
Gantry rotation speed
Should approximate the slide thickness of
PET (e.g. 4-5 mm)
Slower rotation speed helps blur cardiac
motion (e.g. 1 sec/revolution of slower
Relatively high pitch (e.g. 1:1)
ECG gating is not recommended
80-140 kVp, depending on manufacturer
Because the scan is only acquire for AC,
low tube current is preferred (10-20 mA)
End-expiration breathhold or shallow
freebreathing is preferred
Should approximate the slice thickness of
PET (e.g. 4-5 mm)
Slower gantry rotation
increase radiation dose
Inversely related to pitch
to ensure proper registration between transmission
and emission scans for quality assurance and proper
interpretation of PET images. Several approaches are
currently being devised to reduce misregistration
artifacts, such as reducing CT tube current and
increasing the duration CT acquisition to better
match the temporal resolution between the
attenuation and emission maps.22,23
3. Metal artifacts can present a challenge for the
reconstruction algorithm and must be compensated
for to produce accurate attenuation maps.24,25
Although pacemaker leads do not appear to cause
artifacts in cardiac PET/CT images, automatic
implantable cardioverter defibrillator leads frequently
do result in artifacts of sufficient magnitude to impact
clinical image interpretation.24 Ideally, stress
transmission scans should be acquired during peak stress or
vasodilation, although this is not practical.
As such, the technologist and physician must
carefully inspect the transmission and emission image sets to
ensure that they are properly registered in the transaxial,
sagittal, and coronal planes. For patients undergoing PET/
CT, a separate, CT-based transmission scan for correction
of the stress images is standard. For 82Rb, a post-stress
transmission scan is preferred to minimize misregistration
artifacts on the corrected 82Rb images when
misregistration compensation software is not available.
PET MYOCARDIAL PERFUSION IMAGING
PET MPI is an important diagnostic and prognostic
technique in the assessment of patients with known or
suspected CAD. The goal of evaluating myocardial
perfusion with PET imaging is to detect physiologically
significant coronary artery narrowing to guide clinical
management of patients with known or suspected CAD
and those without overt CAD but with cardiovascular
risk factors in order to:
• evaluate the progression of atherosclerosis,
• determine cause of ischemic symptoms and
recommend medical or revascularization therapy,
• estimate the potential for future adverse events, and
• improve patient survival.
Stress and rest paired myocardial perfusion studies are
commonly performed to assess myocardial ischemia and/
or infarction. Current Food and Drug Administration
(FDA)-approved and CMS-reimbursable PET MBF
tracers are limited to 82Rb and 13N-ammonia. While 15O-water
is also used clinically in Europe, it is not FDA approved in
the United States. There are also 18F-labeled MBF agents
that are currently investigational and in clinical trials.
Normal myocardial perfusion on stress images
implies the absence of physiologically significant
CAD. Abnormal myocardial perfusion on stress images
suggests the presence of significantly narrowed coronary
arteries. However, it is important to point out that such
visual interpretation of relative radiotracer uptake may
underestimate balanced reduction in blood flow in all
three vascular territories, also termed ‘‘balanced
ischemia.’’ Routine assessment of absolute quantitative MBF
may identify such patients as well as those with
equivocal or borderline radiotracer uptake defects. If
the stress-induced regional perfusion defect persists on
the corresponding paired rest images, it suggests the
presence of an irreversible myocardial injury. On the
other hand, if the defect on the stress images resolves
completely or partially on the rest images, it suggests the
presence of stress-induced myocardial ischemia.
Absolute quantitative MBF may provide further insight into
coronary steal phenomenon, defined as an absolute
decrease in vasodilator stress perfusion from resting
blood flow in collateral-dependent myocardium as well
as in hibernation. Low resting MBF may or may not
increase with stress but is nonetheless viable requiring
an assessment of myocardial metabolism. In the case of
hibernation, imaging of myocardial perfusion can be
combined with myocardial metabolism imaging with
18F-FDG for the assessment of myocardial viability in
areas of resting hypoperfusion and dysfunctional
Patient preparation is similar to preparation for stress
and rest myocardial perfusion SPECT imaging. This
includes fasting for 6 hours or more, with the exception
of water intake. Patients should avoid caffeinated
beverages for at least 12 hours, and avoid
theophyllinecontaining medications for at least 48 hours.26
Cardiac Stress Testing
Details of pharmacologic or exercise stress testing
are beyond the goals of this document. Nonetheless,
stress protocols are, for the most part, generic for all
perfusion agents.26 The specific differences in
acquisition protocols for 82Rb and 13N-ammonia imaging are
related to the duration of uptake and clearance of these
radiopharmaceuticals, their physical half-lives, and the
characteristics of the vasodilators used for the study. For
example, the time course of action of the A2A-selective
adenosine receptor agonist, regadenoson, is longer than
that of adenosine (peak-effect onset at *1 min post
bolus injection with a duration of approximately 8 to 10
minutes at C80% peak effect).27 As such, accurate
quantification of MBF is critically dependent on the
interplay between the vasodilator and the timing of the
radiotracer injection in relation to the peak coronary
vasodilation achieved by the drug.28–31 In addition, all
contraindications for performing cardiac stress testing
with SPECT also apply to PET.31
82Rb Perfusion Imaging
Tracer properties. 82Rb PET MPI is a
wellestablished and highly accurate technique for the
diagnosis of hemodynamic CAD.32–34 82Rb is a monovalent
cationic analog of potassium. It is produced in a
commercially available generator by decay from 82Sr
attached to an elution column. 82Sr has a half-life of 25.5
days and decays to 82Rb by electron capture. 82Rb
decays with a physical half-life of 75 seconds by
emission of several possible very high-energy positrons.
The resulting long positron range worsens image
resolution compared to 18F and 13N. The daughter product is
krypton-82, which is stable. The 82Sr-containing
generator is commercially available and is replaced every 6
weeks, thus obviating the need for a cyclotron.
82Rb is eluted from the generator with 10 to 50 mL
of normal saline by a computer-controlled elution pump,
connected by intravenous (IV) tubing to the patient. The
generator is fully replenished every 10 minutes. While
the short half-life of 82Rb challenges the performance
limits of PET scanners, it facilitates the rapid completion
of a series of rest and stress myocardial perfusion studies.
82Rb is extracted from plasma with high efficiency
by myocardial cells via the Na/K adenosine
triphosphatase pump. Its first-pass extraction is considerably
less than that of 13N-ammonia, and decreases rapidly
with increasing blood flow. 82Rb extraction can be
decreased by severe acidosis, hypoxia, and
ischemia.35–37 Thus, while uptake of 82Rb predominantly
depends on MBF, it may be modulated by metabolism
and cell membrane integrity.
Dosimetry. The radiation dosimetry from 82Rb in
an adult may vary from 1.1 to 3.5 mSv total effective
dose for a maximal allowable activity of 60 mCi
injection for each rest and stress study.38,39 With current
advances in PET instrumentation, diagnostic quality
PET images can be acquired using only 20 to 40 mCi of
82Rb for each of the rest and stress images of the study
resulting in lower radiation exposure.
Scout scanning. Scout scanning is
recommended before each injection to ensure that the patient
is correctly positioned and is not exposed to unnecessary
radiation. This can be done with a fast transmission scan
or with a low-dose 82Rb injection (10 to 20 mCi). The
low-dose 82Rb scout scan is also used to estimate
circulation times and cardiac blood pool clearance times,
which assist in selection of the optimum
injection-toimaging delay time between 82Rb injection and initiation
of acquisition of myocardial 82Rb images. However,
given the growing literature regarding the incremental
value of absolute MBF measurement to the visual
interpretation of relative radiotracer uptake, it is strongly
recommended that the default acquisition be set at
dynamic list mode, thereby allowing the user to have the
option of interpreting visual and/or quantitative data.
With PET/CT systems, a low-dose x-ray scout scan is
routinely used for patient positioning.
Imaging parameters. Rest imaging should be
performed before stress imaging to reduce the impact of
residual stress effects (e.g., stunning and steal). For
82Rb, about 80% of the useful counts are acquired in the
first 3 minutes, 95% of the useful counts are obtained in
the first 5 minutes, and 97% are obtained in the first 6
minutes. The patient should be infused with 82Rb for a
maximum of 30 seconds. After the dose is delivered,
patients with normal ventricular function, or left
ventricular ejection fraction (LVEF) [50%, are typically
imaged starting 70 to 90 seconds after the injection. For
those with reduced ventricular function, or LVEF from
30 to 50%, imaging usually is begun 90 to 110 seconds
after termination of the infusion. Those with poor
function, or LVEF \30%, are typically imaged at 110 to
130 seconds. Excessive blood pool counts can scatter
into myocardial counts, impacting defect size and
severity (Tables 6 and 7).
13N-Ammonia Perfusion Imaging
13N-ammonia is a valuable agent for measuring
either absolute or relative MBF.40,41 For measurements
of absolute MBF, dynamic acquisition from time of
injection is required, followed by applying 2- and
3compartment kinetic models that incorporate both
extraction and retention rate constants. In a clinical
setting, 13N-ammonia PET myocardial perfusion images
are assessed visually or semiquantitatively along with
absolute MBF measurements with commercially
available software for the evaluation of regional myocardial
13N-ammonia is an extractable myocardial
perfusion tracer that has been used extensively in scientific
investigations with PET for more than three decades. At
physiologic pH, 13N-ammonia is in its cationic form
with a physical half-life of 10 minutes. Its relatively
short half-life requires an on-site cyclotron and
radiochemistry synthesis capability. 13N decays by positron
emission. The daughter product is carbon-13, which is
stable. Myocardial uptake of 13N-ammonia depends on
flow, extraction, and retention. First-pass myocardial
extraction of 13N-ammonia is related inversely and
nonlinearly to blood flow47 Following this initial extraction
BGO Systems LSO (LYSO) Systems
40-60 mCi (1480-2220 MBq)
10-20 mCi (370-740 MBq) 30-40 mCi (110-1480 MBq)
Bolus of ≤30 seconds
LVEF >50%: 70-90 seconds
LVEF <50% or unknown: 90-130 seconds
List mode: acquire immediately
Use scout scan: 10-20 mCi (370-740 MBq) 82Rb
Use transmission scan
List mode: gated/dynamic (no delay after injection)
Gated acquisition (delay after injection
Measure attenuation correction, before or after
FBP or iterative expectation maximization (e.g. OSEM)
20 mCi (740 MBq)
Bolus of ≤30 seconds
LVEF >50%: 70-90 seconds
LVEF <50% or unknown: 90-130 seconds
List mode: acquire immediately
Longer delays than the above must be used if count rate at these
times exceeds the maximum value specified by the manufacturer
Use scout scan: 10-20 mCi (370-740 MBq) 82Rb
Use transmission scan
List mode: gated/dynamic (no delay after injection)
Measure attenuation correction, before or after
Iterative row-action maximum likelihood algorithm (3D-RAMLA)
across the capillary membrane, 13N-ammonia may cross
myocardial cell membranes by passive diffusion or as an
ammonium ion by the active sodium-potassium
transport mechanism. Once in the myocyte, 13N-ammonia is
either incorporated into the amino acid pool as
13Nglutamine or back-diffuses into the blood. The
myocardial tissue retention of ammonia as 13N-glutamine is
mediated by adenosine triphosphate and glutamine
synthetase. Thus, uptake and retention can both be
altered by changes in the metabolic state of the
myocardium, although the magnitude of metabolic
effects on the radiotracer retention appears to be small.
Dosimetry. The radiation dosimetry from a 20
mCi dose of 13N-ammonia is 1.48 mSv total effective
dose in an adult.48 The critical organ is the urinary
bladder, which receives 6 mSv from a 20 mCi dose of
13N-ammonia.48 The dosimetry is relatively low, due to
the short half-life of 13N and the low energy of the
Acquisition parameters. Table 8 summarizes
the recommended guidelines for performing
13N-ammonia perfusion scans with dedicated, multicrystal PET or
PET/CT cameras for rest and stress PET MPI for the
diagnosis and evaluation of CAD, or as part of an
assessment of myocardial viability.
Dose. Typically, 10 to 20 mCi of 13N-ammonia is
injected. Large patients may benefit from higher, 25 to
30 mCi, doses. In addition, the dose of radioactivity
administered will also depend on whether images are
obtained in 2D or 3D imaging mode.
15O-water is often considered the ideal radiotracer
for quantifying MBF in absolute terms.49–53 Because the
capillary and sarcolemmal membranes do not exert a
barrier effect on the exchange of water, the activity of
15O-labeled water observed in an assigned region of
interest to the myocardium on the serially acquired
images can be described by a one-compartment tracer
kinetic model. 15O-water is not FDA approved, and
therefore it is not used clinically in the United States. It
is, however, used in Europe for clinical imaging. Initial
studies with 18F-labeled MBF agent, flurpiridaz, in
humans has shown a very good diagnostic accuracy for
the detection of significant CAD.34 Regarding its
potential for quantification of absolute MBF, in an
experimental study, measurement of the standardized
uptake value (SUV) obtained at 5 to 10 minutes after
Reconstructed pixel size
10-20 mCi (370-740 MBq) typical
Over 20-30 second infusion
1.5-3 minutes after end of infusion
Start camera prior to dose infusion
18F-flurpiridaz IV injection showed a linear correlation
with adenosine hyperemia MBF as quantified by
IMAGE DISPLAY, NORMALIZATION, AND
EVALUATION FOR TECHNICAL ERRORS
Recommendations for display of PET perfusion
rest-stress and/or perfusion/metabolism images are
consistent with those listed in previous guidelines for
reststress SPECT MPI.55 It is necessary to examine the
transaxial, coronal, and sagittal views for assessing the
alignment of the emission images acquired during stress,
rest, and metabolism, as well as the transmission images.
Fused transmission and emission images are preferred.
Images that are not aligned (e.g., due to patient or
cardiac motion) may cause serious image artifacts,
especially when only one set of attenuation correction
images has been applied to all emission images for
attenuation correction. This is a problem particularly
when CT is used for attenuation correction.19 It is
important that the fusion images be reviewed for
potential misalignment problems and appropriate
adjustments are made. Some vendors’ systems now provide
software that allows realignment of transmission CT and
emission PET images before processing, and in other
instances image data can be transferred to a standalone
PC that has realignment software.
The reoriented images should be displayed as
1. A short-axis view, by slicing perpendicular to the
long axis of the LV from apex (left) to base,
2. A vertical long-axis view, by slicing vertically from septum (left) to lateral wall, and
3. A horizontal long-axis view, by slicing from the
inferior (left) to the anterior wall.
For interpretation and comparison of perfusion and
metabolism images, slices of all datasets should be
displayed aligned and adjacent to each other. In the
absence of motion artifact, combined assessment of
perfusion and metabolism within a single PET session
offers the advantage of copying the ventricular long axis
defined during image orientation from one image set to
the second set, thereby optimizing the matching of the
perfusion with the metabolism images. Normalization of
the stress and rest perfusion image set is commonly
performed using the maximal myocardial pixel value in
each of the two or three image sets, or, for example, the
average pixel value with the highest 5% of activity of
the perfusion images. Each perfusion study is then
normalized to its own maximum.
The metabolism images are normalized to the
counts in the same myocardial region on the resting
perfusion images (e.g., with the highest count rates that
were obtained on the perfusion study).56,57 An important
limitation of this approach, however, is that glucose
metabolism may be enhanced or abnormally increased
in regions with apparently normal resting myocardial
perfusion, if such regions are subtended by significantly
narrowed coronary arteries and are in fact ischemic on
stress myocardial perfusion studies.58 Moreover, visual
assessment of resting myocardial uptake of the
radiotracer reflects the distribution of MBF in ‘‘relative’’
terms (i.e., relative to their regions of the LV
myocardium) and not in ‘‘absolute’’ terms (i.e., mL/min/gm
myocardial tissue). Thus, in some patients with
multivessel CAD, it is possible that all myocardial regions are
in fact hypoperfused at rest in ‘‘absolute’’ terms (i.e.,
characterized as balanced reduction in blood flow) and
yet appear normal in ‘‘relative’’ terms. Quantitative
resting MBF may be used to define the region with the
highest absolute MBF for normalization of the
metabolism data. Whether absolute quantification of regional
myocardial glucose utilization may also aid in this
distinction is not well established in the literature. If
stress myocardial perfusion PET images are available, it
is recommended that the normal reference region on
stress perfusion images be utilized.40 In the presence of
left bundle branch block (LBBB), where the septal
18FFDG uptake is spuriously decreased, the septum should
not be used as the site for normalization. Accordingly,
the ECG should be reviewed in conjunction with
The standard segmentation model divides the LV into
three major short-axis slices: apical, mid-cavity, and
basal. The apical short-axis slice is divided into four
segments, whereas the mid-cavity and basal slices are
divided into six segments. The apex is analyzed
separately, usually from a vertical long-axis slice. Although
the anatomy of coronary arteries may vary in individual
patients, the anterior, septal, and apical segments are
usually ascribed to the left anterior descending coronary
artery, the inferior and basal septal segments to the right
coronary artery, and the lateral segments to the left
circumflex coronary artery. The apex can also be supplied
by the right coronary and left circumflex artery. Data from
the individual short-axis tomograms can be combined to
create a polar map display, representing a 2D compilation
of all the 3D short-axis perfusion data. The 2D
compilation of perfusion and metabolism data can then easily be
assigned to specific vascular territories. These derivative
polar maps should not be considered a substitute for the
examination of the standard short-axis and long-axis
cardiac tomographic slices.
If suitable software is available, reconstructed
myocardial perfusion and metabolism datasets can be
displayed in a 3D static or cine mode, which may be
convenient for morphologic correlation with
angiographic correlation derived from CT, MR, or
conventional angiography. Some of the software may
allow the overlay of the coronary anatomy on the 3D
reconstructed perfusion and metabolism images of the
heart. An advantage of 3D over conventional 2D
displays with regard to accuracy of PET image
interpretation has not been demonstrated.
Recommended Medium for Display
It is strongly recommended for the interpreting
physician to use the computer monitor rather than film
hard copies for interpretation of myocardial perfusion
and metabolism images. The latter would be especially
important for gated PET images, where dynamic wall
motion data are viewed for proper interpretation of
regional abnormalities. A linear gray scale,
monochromatic color scale, or multicolor scale can be used as the
type of display, depending on user experience and
Patient motion. PET images are typically
generated with non-moving circular arrays of scintillation
detectors that acquire all projection data simultaneously.
In contrast, SPECT imaging with rotating gamma
cameras—in which patient motion leads to a typical
misalignment between adjacent projection images—can
be identified by viewing a projection movie. Movement
during static PET imaging affects all projections and is
therefore more difficult to identify. Substantial patient
motion can produce blurring of image contours.
Therefore, attention to patient motion during image
acquisition is essential to minimize motion artifacts.
Patient positioning before and immediately after
image acquisition should be carefully evaluated (e.g., by
checking the alignment of the camera’s positioning laser
beams with ink markers on the patient’s skin).
Acquisition of a scout scan after injection of a small dose,
usually one-third of the standard dose of 82Rb, may
facilitate accurate patient positioning. With PET/CT
systems, a low-dose x-ray scout scan (10 mA) is
routinely used for accurate patient positioning. In
instances of patient discomfort and likely patient
motion, especially during longer image acquisition
times, one approach to reduce the potential for motion
artifacts is to acquire a series of 3 to 4 sequential image
frames instead of a single static image of longer
duration. Dynamic imaging would also be effective for
this purpose. If the quality of one of the serially acquired
frames is compromised by motion, then that frame can
be rejected and only frames that are of acceptable quality
and are free of motion artifacts are summed for the final
Vertical and transaxial displacement of the heart
can occur even in the absence of chest movement. The
latter is perhaps related to the change of breathing
pattern, which may occur during pharmacologic stress.
This could be thought of as analogous to the ‘‘upward
creep’’ phenomenon seen in SPECT imaging. As a
result, under-correction artifacts due to the lower
attenuation coefficient of the overlapping lung tissue may
appear in the anterior or anterolateral regions, or
overcorrection artifacts due to the higher attenuation
coefficients of the overlapping subdiaphragmatic tissues may
appear in the inferior region as hot spots. Inspection of
fused emission-transmission images for possible
misalignment is essential because the resulting artifacts
would greatly affect image interpretation. Fused images
should be inspected in the axial (lateral displacement),
coronal (vertical displacement), and sagittal (vertical
displacement) slices. Alternatively, displacement can be
detected on transaxial images by counting the number of
pixels by which the cardiac image is displaced between
resting-and-stress transaxial acquisitions. Identification
of vertical and lateral displacements that result in
misalignment between the emission and transmission
images is relatively straightforward.
The degree of co-registration of transmission and
emission images should be carefully examined using the
fusion software available on integrated PET/CT systems
to assess the reliability of images with attenuation
correction. If there is patient motion, the cardiac
silhouette may not superimpose perfectly on the
transmission and emission images. If the transmission or
emission scans are degraded by motion during the
acquisition, software may not correct the image quality
and the scan may have to be repeated. In general,
vertical misalignment is easier to resolve by offsetting
the alignment between the emission and transmission
scans, but this option is not generally available. When
the transmission scans are acquired using CT, the
incidental findings in the portion of the chest in the
FOV should be reported, when relevant to patient care.
Reconstruction artifacts. Image artifacts may
occur if extra-cardiac activity is present, adjacent to the
myocardium. For example, intense focal activity in the
liver or the gastrointestinal tract may lead to spillover of
residual activity from imperfect scatter compensation,
resulting in artificially elevated counts, or cause a
reconstruction (i.e., ramp filter) artifact resulting in
apparent low count rates in adjacent myocardium. While
these artifacts are common in SPECT imaging, they are
rare in PET imaging. Additional artifacts can result from
problems with CT transmission images, such as streaks
caused by insufficient x-ray tube intensity in obese
individuals, truncations, beam hardening resulting from
bone (e.g., arms down) or metal adjacent to the heart
(e.g., pacemakers and internal defibrillators), and
breathing leading to disconnected pieces of liver in the lungs
or misalignment between CT and PET data. CT artifacts
are propagated into the PET images through the use of
CT image for attenuation and scatter corrections. These
artifacts are less of a problem with 137Cs attenuation
Image count statistics. The final count density
of PET images is influenced by additional factors, such
as body habitus and weight, radionuclide dose, scanner
performance, acquisition time, and in the case of
metabolic imaging, the dietary and neurohormonal state
of the patient. Image count density directly affects the
diagnostic quality and reliability of the study.
The rest and stress perfusion and/or metabolism
images should be interpreted initially without clinical
information in order to minimize any bias in study
interpretation. All relevant clinical data should be
reviewed after a preliminary impression is formed.
LV and RV size. The reader should note whether
there is an enlargement of the right ventricle (RV) or LV
at rest or whether there is transient stress-induced LV
cavity dilatation. Ventricular enlargement seen on the
stress and rest perfusion or metabolic images generally
indicates left, right, or bi-ventricular dysfunction. LV
and RV sizes, as well as any changes associated with
stress, are typically described qualitatively. A number of
commercially developed software packages originally
developed for SPECT have the ability to quantify mean
LV volumes and end-diastolic and end-systolic volumes
for gated PET images, but not all such packages have
been validated for all PET instruments. Among other
considerations, PET stress images are acquired at the
peak of pharmacologic stress, as opposed to SPECT for
which images are acquired 15 to 45 minutes after stress.
Lung uptake. Increased tracer activity in the
lungs should be reported qualitatively. Increased lung
uptake on the perfusion images, particularly when
severe, may reflect severe LV dysfunction with
increased LV end-diastolic and capillary wedge
pressures. It can also reflect infiltrative diseases of the lungs,
and can be seen in smokers. Increased lung uptake can
adversely affect image quality, and in particular may
interfere with interpretation of the lateral wall. It may be
necessary to increase the time between injection and
image acquisition from 4-5 minutes to 7-8 minutes.59,60
RV uptake. Increased RV tracer uptake may be
seen both on perfusion and metabolism images in the
presence of pulmonary hypertension with or without
significant RV hypertrophy. Increased RV uptake is
usually assessed relative to the radiotracer uptake in the
LV myocardium. Because the septum is shared by both
ventricles, assessment of increased RV uptake should be
made in relation to other regions of the LV myocardium.
Abnormally increased RV tracer uptake is a qualitative
assessment. When RV uptake relative to the LV is
increased at stress compared to rest, this may indicate
three-vessel or left main disease and balanced ischemia
(indicating a relative reduction in LV perfusion rather
than increased RV perfusion).61
Blood pool activity. Visualization of persistent
blood pool activity on either perfusion or metabolism
images is usually a sign of relatively poor myocardial
uptake of the radiotracer, insufficient time for uptake of
the radiotracer into the myocardium, or diminished
clearance of the radiotracer from blood. A major cause
of increased blood pool activity, especially for perfusion
imaging with 82Rb, is impairment of cardiac systolic
function that prolongs the circulation time. This is
especially relevant when only static images are acquired,
because vasodilators typically increase cardiac output
and shorten the circulation time. List-mode acquisition
allows for the reprocessing of images with varying delay
times and may be useful for optimizing the quality of
Extra-cardiac findings. The tomographic images
should be carefully examined for uptake of the radiotracer
in organs other than the myocardium, particularly in the
lungs and the mediastinum. Extra-cardiac uptake of a flow
tracer may be of clinical significance, as it may be
associated with malignancy and/or an inflammatory
process. The 3D maximum intensity projection display,
a method of displaying acquired PET images as a rotating
3D display, can be particularly helpful in this regard.
When using PET/CT systems, review of the
low-resolution CT-based transmission image can be useful to
delineate potentially important ancillary findings, such
as pleural and pericardial effusion, coronary and/or aortic
calcification, breast, mediastinal, or lung mass, and others.
Normal variants. Apparent persistent reduction
of activity at stress and rest can be seen at the apex on
PET perfusion images and is a normal variant related to
a partial volume artifact due to apical thinning relative
to the remainder of the myocardium. This may be seen
with 82Rb or 13N ammonia—often more evident with
13N-ammonia and with TOF cameras. Persistent
reduction at stress and rest in the lateral wall is a common
variant in 13N-ammonia imaging, more evident in a
normal-sized and functioning ventricle. The precise
explanation of this finding has been elusive but appears
to be unique to 13N-ammonia and may relate to
differences in retention or wall motion of the lateral
wall versus the septum.62
Interpretation of PET Perfusion Data
Perfusion defect location, severity, and
extent. Myocardial perfusion defects should be
identified through careful visual analysis of the reoriented
myocardial slices. Perfusion defects should be
characterized by extent, severity, and location relative to the
specific myocardial territory, such as the anterior,
lateral, inferior, septal, and/or apical walls. Standardized
nomenclature should be used, according to previously
published guidelines.63 RV defects due to scarring and
ischemia should be noted.
Qualitative scoring. Defect extent should be
qualitatively estimated by describing the location of the
abnormal segments involved (e.g., anterior, inferior, or
lateral) as well as the extent in the LV (e.g.,
‘mid-todistal’ or ‘extending from base to the apex’). The extent
of the defect may also be qualitatively described as
small (5 to 10% of the LV), medium (10 to 20% of the
LV), or large (20% of the LV). A defect of more than
10% of the LV is associated with a higher risk of cardiac
events. Defect severity is typically expressed
qualitatively as mild, moderate, or severe. Severe defects may
be considered as those having a tracer concentration
equal or similar to background activity, and moderate
defects are considered definitely abnormal but visually
discernable activity above the background. Mild defects
are those with a subtle but definite reduction in regional
myocardial tracer uptake.
Stress and rest myocardial perfusion image sets are
compared in order to determine the presence, extent, and
severity of stress-induced perfusion defects and to
determine whether such defects represent regions of
myocardial ischemia or infarction. Regions with
stressinduced perfusion abnormalities, which have normal
perfusion at rest, are termed reversible perfusion defects
and represent ischemia. Perfusion abnormalities on
stress, which remain unchanged on rest images, are
termed irreversible or fixed defects, and most often
represent areas of prior myocardial infarction. When
both ischemia and scar are present, the defect
reversibility is incomplete, giving the appearance of
Semiquantitative scoring system. In addition
to the qualitative assessment of perfusion defects, a
wellaccepted 5-point scale semiquantitative visual scoring
method is used in direct proportion to the observed count
density of the segment, as follows: 0 = no defect; 1 =
mildly reduced; 2 = moderately reduced; 3 = severely
reduced; 4 = absent activity (Table 9). This approach
standardizes the visual interpretation of scans, reduces the
likelihood of overlooking clinically significant defects,
and provides a semiquantitative index that is applicable to
diagnostic and prognostic assessments.
A 17-segment model for semiquantitative visual
analysis can also be employed.63 The model is based on
three short-axis slices (apical, mid, and basal) to represent
most of the LV and one vertical long-axis slice to better
represent the LV apex (Figure 1). The basal and
midshort-axis slices are divided into six segments. The apical
short-axis slice is divided into four segments. A single
apical segment is taken from the vertical long-axis slice.
Each segment has a specific name. The extent of stress
and rest perfusion abnormalities, as well as an estimate of
the extent of scarring and ischemia, can be performed by
counting the number of segments.
Myocardial segments may be assigned to coronary
artery territories. Caution should be exercised because the
coronary anatomy varies widely among patients. For
example, it is not uncommon to find segments 9, 10, and 15 (of the
17-segment model) involved in left anterior descending
artery disease. Similarly, segments 5 and 11 of the model
may be affected by disease of the right coronary artery.
In addition to individual scores, calculation of
summed scores is recommended, in which the summed
stress score (SSS) is the sum of the stress scores of all
segments, the summed rest score (SRS) is the sum of
the resting scores of all segments, and the summed
difference score (SDS) is the difference between the
summed stress and summed rest scores and serves as a
measure of reversibility. The summed scores
incorporate the global extent and severity of perfusion
abnormality. For example, the SSS reflects the extent
and severity of perfusion defects at stress and is
affected by prior myocardial infarction as well as by
On the other hand, the SRS reflects the amount of
infarcted and/or hibernating myocardium. The SDS is a
measure of the extent and severity of stress-induced
Before scoring, it is necessary for the interpreting
physician to be familiar with the normal regional
variation in count distribution of myocardial perfusion
PET. No regional variation in tracer uptake has been
reported for 82Rb, except for a mild reduction in the
apex and base of the LV, consistent with segmentation
artifact and/or thinning of the LV myocardium in these
locations. Regarding 13N-ammonia, unlike 82Rb and
other SPECT perfusion tracers, the lateral wall uptake
may not necessarily be the region with the highest
counts, serving as the reference region for
normalization. This normal variation should be kept in mind
when visually interpreting lateral perfusion defects with
13N-ammonia PET.62 Absolute quantitative MBF of the
lateral wall has been shown to further differentiate a
true perfusion defect from normal variant in the
clinical setting. In addition, apical thinning may be
more pronounced with TOF 13N-ammonia imaging.
Given the variability in the normal distribution of
various radiotracers, the patient’s polar map may be
compared with a reference polar map derived from
radiotracer and gender-specific normal database.
Ideally, each camera system and acquisition protocol
should have its own ‘‘normal’’ file but such normal
databases are not widely available. The
semiquantitative analysis system provided by a specific vendor
should be validated by appropriate studies published in
Absolute quantification of myocardial
blood flow. Quantitative blood flow approaches offer
an objective interpretation that is inherently more
reproducible than visual analysis.64–66 Absolute
quantification may aid in assessing the physiologic
significance of known coronary artery stenosis,
especially when of intermediate severity. Both relative and
absolute quantification are particularly useful in
describing changes between two studies in the same
patient. In addition, quantitative measurements of MBF
may identify balanced reductions in MBF due to
balanced multivessel CAD or diffuse small-vessel
Software packages that are commonly used for
quantitative analysis of SPECT perfusion images have
been developed for PET.67 These analyses portray
relative uptake of tracer in reference to limits derived
from PET images (82Rb or 13N-ammonia) of patients
with a low likelihood of coronary disease, but do not
present true blood flow quantitation values. High
diagnostic accuracy for detecting obstructive CAD has been
reported.68,69 Similar to SPECT, PET total perfusion
deficit values for stress, rest, and defect reversibility
(i.e., ischemia) can be derived, but use of these
parameters to guide patient management has not been
established. The various analytic software packages also
provide quantitative data for LV volumes and ejection
fractions. As is the case with SPECT, it must be
recognized that different packages do not provide the
same values, something that must be understood when
deciding whether a finding is normal or abnormal, as
well as when repeat images are done for a patient using
different analytic software.70
Quantitative absolute hyperemic MBF in mL/min/
gm tissue and flow reserve (representing the ratio of
hyperemic and resting MBF)—derived from dynamic
acquisition with measurements of resultant myocardial
and blood pool time-activity curves—is a potentially
powerful adjunct to PET perfusion imaging. It is
important to recognize, however, that myocardial flow
reserve (MFR) ratio can be spuriously lowered by
elevated resting blood flow in the denominator, as seen
in patients with hypertension or high resting
ratepressure product. Thus, it is important to interpret both
hyperemic MBF and flow reserve in all subjects. Among
the promises of quantitative blood flow measurements
are improved diagnostic accuracy, including the ability
to overcome false-negative studies in the setting of
balanced ischemia and improved risk
stratification.63,71–75 Quantitative MBF can be assessed globally
As with all nuclear cardiology techniques,
attention to quality control (e.g., assessment of
timeactivity curves) and use of validated methodology and
software packages are crucial. It is also important to
recognize the potential pitfalls when interpreting and
reporting derived quantitative values, including the
influence of various forms of stress, different
radiotracers, characteristics of particular software packages,
and even unique patient idiosyncrasies. In addition, as
with most imaging parameters, MBF values should be
supplements to be considered in conjunction with
patient clinical characteristics and other image
findings when used to diagnose and direct patient
At the present time, quantitative absolute MBF
measurements with PET appear most helpful in:
1. Patients without known prior history of cardiac disease who present with symptoms suspicious for myocardial ischemia.
2. Patients with known CAD, in whom more specific physiological assessment is desired.
3. Identifying an increased suspicion for multivessel CAD.
4. Situations with a disparity between visual perfusion abnormalities and apparently normal coronary angiography, in order to assess possible microvascular dysfunction.
5. Heart transplant when there is a question of
In contrast, there are particular patients for whom
reporting hyperemic blood flow or flow reserve may not
add diagnostic value or can be ambiguous or
1. Patients post-CABG who can have diffuse reduction on MBF despite patent grafts.
2. Patients with large transmural infarcts where resting flow may be severely reduced such that small increases in flow lead to normal or near-normal flow reserve.
3. Patients with advanced severe chronic renal dysfunction who likewise often have diffuse coronary disease.
4. Patients with severe LV dysfunction.
While hyperemic blood flow and flow reserve
values may predict worse prognosis, it is already known
that patients with prior CABG, prior MI, chronic renal
failure, and/or severe LV dysfunction are at higher risk.
Because many patients are referred for diagnosis and
detection of ischemia to determine if revascularization
therapy is an option, reporting flow and flow reserve
under the above circumstances may mislead the
referring physician or healthcare provider.
In addition, because of various potential patient
(e.g., receptor peculiarities) and external reasons (e.g.,
unappreciated caffeine intake), a patient can be a
nonresponder to vasodilator stress, with a global MFR at or
about 1. In such circumstances, the visual perfusion
image findings may be invalid. Also, the stress portion
of the test may need to be repeated ensuring no caffeine,
or using another pharmacologic stress imaging agent.
While some variations in cut-off values have been
reported for different tracers and different software, at
the present time it is generally accepted that MFR values
can be interpreted as follows (with small variation
depending on software):
1. MFR [2.3 indicates a favorable prognosis (assuming
that there is no lower regional value).
2. MFR \1.5 suggests significantly diminished flow
reserve (in the absence of concomitant elevated
resting blood flow), and is associated with elevated
Quantitative assessment of MBF in absolute units
(e.g., mL/min/gm tissue) has been well established
in the literature with 13N-ammonia and
15Owater.40–42,44,49–51,64 It requires the acquisition of
images in dynamic mode. The use of list-mode
acquisition enables flow quantification in conjunction with
perfusion and gated LV and regional function. The
added value in terms of diagnosis and prognosis is the
subject of active investigation in several centers.
Regions of interest are placed on the LV myocardium
and the LV blood pool and are copied to all serially
acquired images for generation of myocardial tissue and
blood pool time-activity curves. The time-activity
curves are corrected for activity spillover from the
blood pool to the myocardium and for radioactive decay.
They are then fitted with a validated tracer kinetic
model, and estimates of MBF are obtained. Software
programs are also available for generating parametric
polar maps that display regional MBF in absolute units.
Quantification of MBF with 82Rb has been more
challenging because of its 75-second half-life resulting
in noisy myocardial and blood pool time-activity
curves.76,77 Newer software packages have incorporated
mathematical correction and improved quantitation of
82Rb perfusion images. The kinetic behavior 82Rb in
tissue can be described by a one- or two-compartment
model that can be fitted using the arterial input function
(i.e., obtained from the blood pool concentration of the
LV cavity or left atrium) and myocardial time-activity
curves at each segment, or even (with sufficient
statistics) at each pixel.77–82 The parameters of the model,
which include flow, can be estimated using non-linear
regression or other techniques. The variability of flow
estimates can be reduced by fixing certain parameters to
physiologically realistic values.83
Gated PET images. The ability to acquire cardiac
PET images in conjunction with ECG gating is an
important development that has not always been
available, particularly on 3D scanners. As with SPECT,
accurate gating with PET requires regular R-R intervals.
Some systems, however, support ECG-gated imaging via
list-mode acquisition that may allow accurate assessment
of gated LV function in patients with irregular rhythms.
In such a mode, the positions of all coincidence pairs are
recorded along with timing information and input from
an electrocardiogram. These data can be retrospectively
processed to produce ECG-gated images, ungated
images, and if necessary, dynamic images, which
represent the activity distribution as a function of time. The
flexibility of this mode of acquisition is particularly
convenient for quantitative analysis.
ECG gating of the rest and peak-stress myocardial
perfusion images can provide additional information
regarding changes in LV function and volumes.84 Unlike
ECG gating of the post-stress SPECT images, PET
acquisitions take place during peak pharmacologic
vasodilation.84,85 ECG gating of 18F-FDG PET images
can also provide additional information regarding
regional and global LV function and volumes.
PET IMAGING OF GLUCOSE METABOLISM
18F-FDG PET imaging is the only FDA-approved
technique for the assessment of myocardial viability.
Other disease entities in which metabolic imaging with
18F-FDG PET can play an important role include the
detection of inflammation, as in cardiac sarcoidosis, and
for the detection of infections, as in cardiovascular
devices and prosthetic valves. Depending on the disease
process, measurements of glucose metabolism can
reflect the rates of cellular glucose use from either
cardiac myocytes or from pro-inflammatory cells that
infiltrated either the myocardium or the vasculature.
Consequently, PET with 18F-FDG can be used to detect
the increase in glucose metabolism in these cell types in
a host of cardiovascular diseases.
For a given physiologic environment, the cardiac
myocyte consumes the most efficient metabolic fuel as
an adaptive response to meet its energy demands. Under
fasting and aerobic conditions, long-chain fatty acids are
the preferred fuel in the heart as they supply 65 to 70%
of the energy for the working heart, and some 15 to 20%
of the total energy supply comes from glucose.86 In
postprandial conditions, glucose becomes the preferred
energy substrate. This rapid adaptation in substrate use
is an essential component of maintaining normal cardiac
function and is dependent on a host of variables such as
substrate availability, hormonal status, cardiac
workload, and other factors.86–88 In contrast, chronic
adaptations in cardiac myocyte substrate metabolism
occur in response to sustained abnormal stimuli.89–91 For
example, the chronic reduction of MBF levels that occur
with myocardial hibernation leads to an overdependence
on glucose metabolism by the cardiac myocyte. In
general, this metabolic change is adaptive and preserves
cardiac myocyte health. In contrast, the sustained
increases in plasma fatty acids that occur in diabetes
mellitus result in a chronic increase in fatty acid
metabolism and a reduction in glucose use. Although
initially adaptive, this change in metabolism eventually
becomes maladaptive and leads to cardiac dysfunction.
Increased glucose metabolism is a hallmark of
activation of immune cells involved in both innate (e.g.,
monocytes and macrophages) and adaptive (e.g., T and
B cells) immunity.92 The increase in glucose
metabolism is triggered to meet the higher energy demands of
immune cell activation and reflects the stimulation of
key transcriptional and other signaling pathways. Thus,
under pro-inflammatory conditions, such as sarcoidosis
or device infection that are discussed below, the
presence of immune cell infiltration and activation can be
There are numerous radiotracers that can measure
cellular glucose metabolism either directly, such as with
18F-FDG and 11C-glucose, or indirectly, such as
11Cpalmitate and the various 18F fatty acid analogs.
However, this document will only focus on measurements of
glucose metabolism using 18F-FDG because it is the
only metabolic radiotracer that is FDA approved and is
used routinely for clinical purposes. 18F-FDG is used for
the detection of viable myocardium where the increased
cardiac myocyte glucose metabolism is a marker of
cellular viability. More recently, 18F-FDG is used to
manage patients with potential cardiac sarcoidosis,
medium-to-large vessel vasculitis, and cardiac device
infection, where cellular inflammation is central to the
pathogenesis of these disease processes. The
performance of 18F-FDG in these cardiac diseases is discussed
below. It should be noted that 18F-FDG is being used
with increasing frequency to evaluate other
cardiovascular diseases, such as right ventricular imaging due to
pulmonary hypertension and vascular imaging in
atherosclerosis. These applications, however, are
primarily investigational in nature and will not be
18F-FDG metabolic imaging
Tracer properties. FDG competes with glucose
for transport and for phosphorylation by hexokinase.
Different from glucose, the phosphorylated radiotracer,
18F-FDG-6-phosphate does not proceed into glycogen
synthesis or aerobic glycolysis with only minimal
dephosphorylation and return of radiotracer to blood; it is
thus metabolically trapped in tissue. Consequently, its
uptake is reflective of overall glucose uptake. CMS has
approved reimbursement of 18F-FDG for the evaluation
of myocardial viability. 18F is produced in a cyclotron
through the (p, n) reaction, consisting of bombardment
of 18O-enriched water,93 and decays by the emission of a
positron with a half-life of 110 minutes. The low kinetic
energy of the positron, 511 keV, allows the highest
spatial resolution among all PET radionuclides. The
110-minute physical half-life of 18F-FDG allows
sufficient time for synthesis and purification, with its
commercial distribution in a radius of several hours
from the production.
Tracer dosimetry. The effective dose for a
10mCi dose of 18F-FDG administered intravenously is 7
mSv. The critical organ is the urinary bladder wall
which receives an effective dose of 48 mSv.94 Frequent
voiding 1 to 3 hours post-administration is
recommended in order to reduce radiation exposure.
Detection of viable myocardium
Study protocol. Acute and chronic metabolic
adaptation to a temporary or sustained reduction in
coronary blood flow is designed to protect the structural
and functional integrity of the myocardium. Reversible
metabolic changes, as an adaptive measure to sustain
myocardial viability, will occur in the setting of
diminished, but not absent, regional MBF. When MBF is
absent, irreversible metabolic changes will occur
followed by myocardial infarction and cell death.
Consequently, demonstration of preserved glucose
metabolism by 18F-FDG is a marker of myocardial viability.
In general, the lack of glucose metabolism is indicative
of non-viable myocardium. Accurate detection of viable
myocardium is achieved by referencing the level of
myocardial glucose metabolism to the level of MBF.
Typically, the measurements of MBF are performed
with either 82Rb or 13N-ammonia using procedures
described in the PET myocardial perfusion section. If
these radiotracers are not available, MBF can be
separately determined using technetium-99m-labeled
myocardial perfusion SPECT radiotracers.
Measurements of flow should be obtained in the same imaging
session as measurements of myocardial glucose
metabolism, regardless of the blood flow radiotracer that is
used. If blood flow and metabolism data are acquired
within a few weeks or months apart, it is important to
verify that the patient has been stable during that time
interval and there has been no change in symptoms or
medications. Combining the information from the
glucose metabolism and blood flow studies generate
metabolism-flow patterns indicative of viable and
Patient preparation. Because of the marked
flexibility in substrate use by the myocardium,
standardization of the substrate environment is of critical
importance when performing cardiac 18F-FDG PET
imaging. The goals and protocols for standardization of
the substrate environment differ depending upon
whether the clinical indication for the study is to detect
myocardial viability or inflammation. For the evaluation
of myocardial viability with 18F-FDG, the substrate and
hormonal levels in the blood need to favor metabolism
of glucose over fatty acids by the myocardium.56,87,95,96
This maximizes the 18F-FDG uptake in the myocardium,
resulting in superior image quality, and reduces the
regional variations in 18F-FDG uptake that can occur
when imaging under fasting conditions.57 Protocols to
standardize the substrate environment for viability
imaging are shown in Tables 10 and 11.
Standardization is usually accomplished by loading
the patient with glucose after a fasting period of at least
6 hours to induce an endogenous insulin response. The
temporary increase in plasma glucose levels stimulates
pancreatic insulin production, which in turn reduces
plasma fatty acid levels through its lipogenetic effects of
adipocytes and also normalizes plasma glucose levels.
The most common method of glucose loading is
with an oral load of 25 to 50 grams, but IV loading is
also used. The IV route avoids potential problems due to
variable gastrointestinal absorption times or inability to
tolerate oral dosage. Because of its simplicity, most
laboratories utilize the oral glucose-loading approach,
with supplemental insulin administered as needed. The
physician should take into account whether or not the
patient is taking medications that may either antagonize
or potentiate the effects of insulin.
Diabetic patients. Diabetic patients pose a
unique challenge, either because they have limited
ability to produce endogenous insulin or because their
cells are less able to respond to insulin stimulation. For
this reason, the simple fasting/oral glucose-loading
paradigm is often not effective in diabetic patients.
Use of insulin along with close monitoring of blood
glucose (Table 11) yields satisfactory results. Improved
18F-FDG images can also be seen when image
acquisition is delayed 2 to 3 hours after injection of the
18FFDG dose. Of course, the latter comes at the expense of
increased decay of the radiopharmaceutical. An
alternative technique is the euglycemic-hyperinsulinemic
clamp, which is a rigorous and time-consuming
procedure.96 However, it allows close titration of the
metabolic substrates and insulin levels, which results
Steps for standardization
Step 1: Fast patient
Step 2: Check blood glucose (BG) and the glucose load
(choose one of the following 3 options)
Option 1: Oral glucose loading
IF: fasting BG <~250 mg/dL (13.9 mmol/L)
1) oral glucose load: typically 25-100 g orally, (see Table 11)
2) monitor BG (see Table 11)
IF: fasting BG > ~250 mg/dL (13.9 mmol/L)
THEN: see Table 11
Option 2: Dextrose IV infusion
See details, sample protocol, Appendix
Option 3: Acipimox
Acipimox, 250 mg orally not available in the US
Step 3: Administer18 F-FDG
Time: Dependent on which option was selected
Standard IV administration of 18F-FDG, see Table 12, item 1
0-90 minutes post 18F-FDG injection, see Table 12
BG at 45-60 min after administration Restorative measure Technique
130-140 mg/dL (7.22-7.78 mmol/L) 1 U regular insulin IV Standard
140-160 mg/dL (7.78-8.89 mmol/L) 2 U regular insulin IV
160-180 mg/dL (8.89-10 mmol/L) 3 U regular insulin IV
180-200 mg/dL (10-11.11 mmol/L) 5 U regular insulin IV
> 200 mg/dL (>11.11 mmol/L) Notify physician
BG = blood glucose; FDG = fluorodeoxyglucose; IV = intravenous; mg = milligram; mmol = millimoles;
L = liter; dL = deciliter; U = unit
in excellent image quality in most patients and allows
absolute quantification of myocardial glucose
utilization. Shorter IV glucose/insulin-loading procedures of
30 minutes have also been used with some success.58
(see ‘‘Protocol’’ section, Appendix).
Acquisition parameters. Acquisition
parameters for 18F-FDG PET cardiac imaging are itemized in
Table 12. If 18F-FDG PET metabolic images are
compared to perfusion images acquired by SPECT, the
interpreter should be mindful that there will be
differences in soft tissue attenuation, image resolution, and
registration problems of images acquired on different
instruments. It should be noted that if a 201Tl- or a
99mTclabeled perfusion tracer is used to assess myocardial
perfusion, there is no need to delay the 18F-FDG PET
images. 201Tl and 99mTc will not interfere with the higher
energy 18F photons. However, with 3D PET imaging, the
99mTc activity can increase dead time and thus decrease
the true counts from the 18F-FDG. If 18F-FDG PET
images are acquired first, then it is necessary to wait at
least 5 half-lives, depending on the dose of 18F
administered, before a low-energy (e.g., 201Tl or 99mTc) SPECT
study is performed. This is because the 511-keV photons
from the PET tracers easily penetrate the collimators that
are commonly used for 201Tl or 99mTc imaging. Iterative
reconstruction (ordered subset expectation
maximization, OSEM, 21 subsets, 2 iterations) is the recommended
method of image reconstruction.
Tracer dose (2D or 3D)
Injection rate (Static)
Injection rate (Dynamic)
Image delay after injection
5-15 mCi (185-555 MBq)
Not critical, bolus to 2 min
Bolus for glucose quantification
45-60 min after injection
(keep constant for repeat studies)
Use an 18F-FDG scout scan Optional
Use transmission scan Standard
PET/CT CT scout scan Standard
Imaging mode 2D or 3D Standard
Static or list mode Standard
Image duration 10-30 min (depending on count rate and dose)
Attenuation correction Measure attenuation correction: before or Standard
immediately after scan
Reconstruction method Iterative expectation maximization (e.g. OSEM) or Standard
Reconstruction filter Sufficient to achieve desired resolution/smoothing, Standard
matched between consecutive studies
Reconstructed pixel size 2-3 mm Preferred
4-5 mm Acceptable
Note: If metabolism imaging is combined with PET perfusion imaging, the same parameters for
patient positioning, attenuation correction, and image reconstruction should be applied.
Dose. Typically, 5 to 15 mCi of 18F-FDG is
injected in a peripheral vein. Injection speed is not
critical (i.e., bolus to 2 minutes). To reduce patient dose
to the bladder, patients should be encouraged to void
frequently for 3 to 4 hours after the study.
Scan start time and duration. It is suggested
to wait for a minimum of 45 minutes before starting the
static 18F-FDG scan acquisition. Myocardial uptake of
18F-FDG may continue to increase, and blood pool
activity to decrease, even after 45 minutes. While
waiting for 90 minutes after the injection of 18F-FDG
may give better blood pool clearance and myocardial
uptake, especially in diabetics or subjects with high
blood glucose levels, this comes at the expense of
reduced count rate. If target-to-background ratio is poor
at 45 to 60 minutes, injecting an additional 1 to 3 units
of insulin (depending on the blood glucose level) and
then waiting for an additional 45 to 60 minutes may
improve the image quality substantially. Scan duration is
typically 10 to 30 minutes. If acquired in 3D mode,
compared with 2D mode with the same machine, a
smaller dose is typically required to achieve the same
total count rate, but the imaging time may or may not be
reduced as a result of count rate limitations and
increased scatter. With some PET cameras, beyond a
certain dose, the 3D mode will actually produce poorer
quality images for the same dose and imaging time than
2D mode. For this reason, it is critical to have fully
characterized the performance of the PET system.
Assessment of myocardial viability.
Detection of viable myocardium plays a central role in the
management of patients with LV dysfunction due to
CAD.97 It is based on the recognition that resting LV
dysfunction may be reversible, attributable to
myocardial hibernation/stunning, and not necessarily due to
myocardial scar. As a consequence, its presence signifies
a different prognosis and mandates a different treatment
paradigm compared with the presence of predominantly
non-viable or irreversible damaged tissue. Indeed, the
importance of differentiating viable from non-viable
tissue is highlighted by the plethora of techniques
currently available to perform this task. Myocardial
metabolism imaging with PET and 18F-FDG uses the
preservation of myocardial glucose metabolism,
particularly in the presence of resting hypoperfusion as a
scintigraphic marker of viable myocardium. It is
accomplished with 18F-FDG as a tracer of exogenous glucose
utilization. The regional myocardial concentrations of
this tracer are compared with the regional distribution of
myocardial perfusion. Regional increases in 18F-FDG
uptake relative to regional MBF (i.e.,
perfusion-metabolism mismatch) signify myocardial viability. In
contrast, a regional reduction in 18F-FDG uptake in
proportion to regional reductions in myocardial
perfusion (i.e., perfusion-metabolism match) signifies
myocardial scar or non-viable tissue. Areas with
maintained perfusion, but diminished 18F-FDG uptake, also
likely reflect regions of jeopardized but viable
myocardium as the perfusion tracers reflect active metabolic
Comparison of myocardial metabolism to
perfusion. The comparison of perfusion and
metabolism images obtained with PET is relatively
straightforward because both image sets are attenuation
corrected. Thus, a relative increase in myocardial
metabolism in regions of reduced perfusion by one
grade or more reflects the presence of
perfusionmetabolism mismatch, hence myocardial viability. In
contrast, a relative decrease in myocardial metabolism
that is in proportion to reductions in regional perfusion
reflects the presence of perfusion-metabolism match,
hence myocardial scar or non-viable tissue. Areas with
maintained perfusion, but diminished 18F-FDG uptake
(termed reverse mismatch), also likely reflect regions of
jeopardized but viable myocardium since the perfusion
tracers reflect active metabolic trapping (Na-K ATPase
system for 82Rb and 13N-glutamine mediated by ATP
and glutamine synthetase for 13N-ammonia).43
Special considerations for combining
SPECT perfusion with PET metabolism
images. In current clinical practice, 18F-FDG PET images
are often read in combination with SPECT myocardial
perfusion images. The interpreting physician should be
careful when comparing the non-attenuation-corrected
SPECT images with attenuation-corrected 18F-FDG PET
images. Myocardial regions showing an excessive
reduction in tracer concentration as a result of attenuation
artifacts, such as the inferior wall in men or the anterior
wall in females, may be interpreted as
perfusion-metabolism mismatches, resulting in falsely positive
perfusionmetabolism mismatches. Two approaches have proved
useful for overcoming this limitation:
1. Because assessment of viability is relevant only in
myocardium with regional contractile dysfunction,
gated SPECT or PET images offer means for
determining whether apparent perfusion defects are
associated with abnormal regional wall motion.
2. Quantitative analysis with polar map displays that are
compared with tracer- and gender-specific databases
(for SPECT images) may be a useful aid to the visual
interpretation. SPECT perfusion images with
attenuation correction are helpful; however, neither
approach is infallible.98,99
For myocardial 18F-FDG images acquired with
ultra-high-energy collimators or with SPECT-like
coincidence detection systems, additional problems may be
encountered, especially when the images are not
corrected for photon attenuation.100–103 Attenuation of the
high-energy 511-keV photons is less than that for the
140-keV photons of 99mTc or the 60- to 80-keV photons
of 201Tl, so that attenuation artifacts are less prominent
for 18F-FDG images and may result in an apparent
mismatch. Furthermore, the lower spatial resolution of
SPECT imaging systems for 18F-FDG imaging,
especially when using high-energy photon collimation and
then comparing with 99mTc or 201Tl images, causes
apparent mismatches for small defects, at the base of the
LV, or at the edges or borders of large perfusion defects.
Such artifacts resulting from the use of different photon
energies can be avoided using dedicated PET systems
for both perfusion and metabolism imaging. Again, use
of ECG-gated imaging to demonstrate normal wall
motion, quantitative analysis through polar map
displays with comparison to radiotracer- and
genderspecific databases of normal may aid in the visual
Absolute myocardial glucose
utilization. Quantitative estimates of myocardial glucose
utilization in absolute units of micromoles of glucose per
minute per gram of myocardium have not been found to aid
in the assessment or characterization of myocardial
viability due to the variability in substrate utilization by the
myocardium, even when 18F-FDG images are acquired
during a hyperinsulinemic-euglycemic clamp.95,96,104
Methods for deriving quantitative estimates of
myocardial metabolism require acquisition of serial
images for 60 minutes that begin with tracer
injection.93,105 ROIs are placed on the myocardium and the
LV blood pool and are copied to all serially acquired
images in order to generate myocardial tissue and blood
pool time-activity curves. The time-activity curves are
corrected for spillover activity from the blood pool into
the myocardium and for radioactive decay. The
timeactivity curves are then fitted with a validated tracer
kinetic model, and estimates of regional myocardial
glucose utilization are obtained in micromoles of glucose
per minute per gram of myocardium. Measurements of
glucose metabolic rates further require determination of
glucose concentrations in arterial or arterialized venous
blood. Similar to myocardial perfusion, parametric
images and polar maps are also available for display of
rates of regional myocardial glucose utilization.
Regional metabolic rates on such parametric images are coded
by a color scale and can be determined non-invasively for
any myocardial region through ROIs assigned to the
Integration of perfusion and metabolism
results. The combined evaluation of regional
myocardial perfusion and 18F-FDG metabolism images allows
identification of specific flow-metabolism patterns that
are useful to differentiate viable from non-viable
myocardium.107–112 It is useful to start with a functional
assessment, ideally from gated PET or SPECT imaging, as
dysfunctional segments are those suitable for evaluation
of myocardial viability. If stress perfusion images as well
as resting perfusion images are available, jeopardized
myocardium can be distinguished from normal
myocardium, and myocardium perfused normally at rest, but
dysfunctional as a result of repetitive stunning, can be
distinguished from myopathic or remodeled myocardium.
Differences in blood pool concentration of tracers
can impact the apparent match or mismatch of perfusion
18F-FDG images. The separate adjustment of threshold
and contrast settings can help compensate for these
Four distinct resting perfusion-metabolism patterns
may be observed in dysfunctional myocardium. Patterns
1–2 are all indicative of viable myocardium, whereas
pattern 3 represents non-viable tissue (Table 13).
If stress and rest perfusion imaging information is
available, it is useful to add an estimate of the extent of
stress-inducible ischemia in regions of normal resting
perfusion and 18F-FDG uptake, in regions with matched
resting perfusion 18F-FDG defects, or in regions with
resting perfusion 18F-FDG metabolic mismatch. The
simultaneous display of stress and rest perfusion and
18F-FDG metabolic images is most helpful but not
available on all display workstations. In circumstances
where only resting perfusion imaging is performed
alongside 18F-FDG metabolic imaging, besides
reporting on the extent of scar and extent of hibernating
myocardium, it is useful to indicate that in the absence
of corresponding stress myocardial perfusion images,
one cannot rule out stress-induced myocardial ischemia.
In circumstances where only stress perfusion
imaging is available in combination with 18F-FDG metabolic
imaging, the following patterns can be found in
segments with contractile dysfunction:
1. Stress perfusion defect with preserved 18F-FDG
uptake indicates ischemic but viable myocardium.
Revascularization is generally appropriate as
myocardial ischemia is a very strong predictor for
recovery of perfusion and function after a successful
revascularization. With stress perfusion and 18F-FDG
metabolic paired images, it is not possible to
differentiate between myocardial ischemia, stunning,
2. Stress perfusion defects associated with proportion
ately decreased or lack of 18F-FDG uptake indicates
scarred or non-viable myocardium, and
revascularization is not recommended.
Qualitative or semiquantitative approaches can be
applied to the interpretation of perfusion-metabolism
patterns. When comparing 18F-FDG metabolism with
perfusion images, it is important to first identify the
normal reference region (the region with the highest
tracer uptake), preferably on the stress myocardial
perfusion images. The extent of mismatch or match defect
may be small (5 to 10% of the LV), moderate (10 to
20% of the LV), or large ([20% of the LV). The
severity of a match defect can be expressed as mild,
moderate, or severe in order to differentiate between
non-transmural and transmural myocardial infarction.
Interpretation of 18F-FDG images when
perfusion images have not been obtained.
Interpretation of 18F-FDG images without perfusion images
and/or angiographic information and/or without
information on regional wall motion is discouraged. The
presence of relatively well-preserved 18F-FDG uptake
in dysfunctional myocardium does not differentiate
ischemic from non-ischemic cardiomyopathy. The
Myocardial blood flow
Normal blood flow
Reduced blood flow
Proportionally reduced Proportionally reduced 18F-FDG
blood flow uptake
The first 3 patterns represent viable myocardium. Only the last pattern, where both perfusion and
metabolism defects are matched, represents nonviable (scarred) tissue
May occur in the septum of
patients with LBBB114
degree of 18F-FDG accumulation over and above
regional perfusion helps assess the relative amount of
scar and metabolically viable myocardium. The latter
information may significantly influence the power of the
test for predicting functional recovery. Therefore, it is
recommended that 18F-FDG metabolic images be
analyzed in conjunction with perfusion images, obtained
either with SPECT or, preferably, with PET.
DETECTION OF INFLAMMATION AND
18F-FDG imaging is becoming an accepted tool for
diagnosing active cardiac inflammation.114,115 While the
technique is potentially useful in a variety of
inflammatory conditions, such as giant cell myocarditis116 and viral
myocarditis,117 currently the predominant use is for
identification of active cardiac sarcoidosis. Another
emerging application is for identification of
cardiovascular infections, particularly prosthesis and device infection.
Assessment of Cardiac Sarcoidosis
Sarcoidosis with cardiac involvement indicates a high
risk of mortality and morbidity, accounting for 13% to 25%
of fatal cases118,119 with a reported five-year mortality
ranging from 25% to 66%.119,120 Signs and symptoms can
be non-specific with autopsies showing more prevalent
cardiac involvement than is appreciated clinically.121
While a clinical diagnosis of cardiac sarcoidosis had
customarily been established based on the Japanese
Ministry of Health and Welfare Diagnostic Guidelines
(JMHW)122 as revised by the Japan Society of Sarcoidosis
and other Granulomatous Disorders in 2006,123 this
standard relies on biopsy-proven cardiac involvement or
histologically proven extra-cardiac disease with indirect
findings of cardiac inflammation.124 Unfortunately,
cardiac biopsy has limited sensitivity. Indirect evidence
consisted of cardiac 67Ga (gallium citrate) uptake, a
perfusion defect consistent with myocardial scarring,
cardiac wall motion abnormalities, conduction
abnormalities on ECG, and more recently abnormalities on cardiac
MR.125 Most recently, the value of cardiac 18F-FDG PET
imaging for assessment of active cardiac sarcoidosis has
been demonstrated and in many places is becoming an
established technique.126–128 The Heart Rhythm Society
has established new criteria for clinical diagnosis of
cardiac sarcoidosis that includes PET imaging.129
The underlying pathophysiologic principle involves
an upregulation of glucose metabolism at sites of
macrophage-mediated inflammation. Diagnostic
accuracy has been shown to be high, with a reported
sensitivity of 89% and a specificity of 78%125 from
meta-analysis of 7 studies.128 18F-FDG PET may be
positive earlier than MR reflecting inflammatory activity
of the disease.130 In addition, strong risk-stratification
power has been demonstrated for 18F-FDG PET that is
beyond that provided by the JMHW criteria.131
Study protocol. When 18F-FDG PET is used for
the detection of cardiac sarcoidosis, a rest perfusion
imaging study is also required for both co-localization
with the myocardium and to determine whether there are
inflammatory cells present (termed mismatched defect) or
absent (termed matched defect) in hypoperfused regions.
For imaging of a cardiovascular device or prosthetic
infections, or medium-to-large vessel vasculitis, however,
a myocardial perfusion study is not required. Other than this
difference in the requirement for a myocardial perfusion
scan, the acquisition, reconstruction, image review, and
reporting of the 18F-FDG PET scan for infection/vasculitis
are the same as for cardiac sarcoidosis.
For cardiac sarcoidosis, it is important to exclude
significant obstructive CAD and prior myocardial
infarction. CAD is excluded, prior to 18F-FDG PET, preferably
by a coronary angiogram (invasive or CT) or rest and
stress MPI. The rest MPI study can be performed with
either PET or SPECT methods. Rest MPI can be
performed on the same day (typically) or on a different
day (as needed) from the 18F-FDG study. If SPECT MPI
is used, attenuation-corrected images are recommended.
MPI is required at baseline and at follow-up scans.
Patient preparation. A key aspect of cardiac
sarcoidosis imaging is proper dietary preparation that
suppresses physiological cardiomyocyte uptake of
18FFDG, such that tracer uptake is limited to active
inflammatory cells in the myocardium (Table 14). The
primary dietary preparation consisting of avoidance of
carbohydrate-containing foods should begin about 24
hours prior to the test, with an intake of high-fat and
highprotein foods for at least two meals 24 hours prior, and
then an overnight fast.132–136 Interpreting physicians
should also be aware of potential confounding factors
such as administration of glucose-containing IV
medications and preparations to hospitalized patients, and less
common activities, such as peritoneal dialysis.
Suppression of myocyte glucose uptake can be assisted by giving
IV unfractionated heparin (10 IU/kg 30 minutes prior ? 5
IU/kg 15 minutes prior or 50 IU/kg 15 minutes prior to
radiotracer administration)137, which results in
elevated138 plasma levels of free fatty acids and increasing
cardiac utilization of free fatty acids instead of glucose,
without increasing partial thromboplastin time. Lower
doses of IV heparin (15 IU/kg) appear to be effective in
suppressing physiological uptake of 18F-FDG without
significant prolongation of partial thromboplastin time.
Although not systematically validated, a
combination of one or more of the above methods appears to be
Preferred for patients on tube
feeds or patients scheduled for
procedures requiring NPO
High fat, protein permitted,
low-to-no carbohydrate diet
Ensure patient has no
administration of IV heparin.*
IV regular heparin drip is
frequently prepared in D5W
and should be discontinued
whenever possible prior to the
sarcoid protocol 18F-FDG
High fat/low carbohydrate diet
IV unfractionated heparin
Two meals 24 hours prior to
the study, followed by an
15-50 units of regular IV
heparin 15 min prior to IV
18FFDG administration or 500 IU
of IV heparin 45 minutes and
15 minutes (total 1000 IU) prior
to IV 18F-FDG
Combined methods High fat/low-carbohydrate diet
for 2 meals, one day prior,
followed by overnight fast,
and IV regular heparin prior to
administration of 18F-FDG
* including bleeding tendencies, allergy or history heparin-induced thrombocytopenia with thrombosis (HIT);
IV = intravenous; NPO = Nil per os, nothing by mouth
better than any single method alone.130 The success rates
of these various methods to suppress the myocardial
glucose utilization are not uniform, and may be difficult
depending on the other factors, such as dietary
compliance, medications, metabolic milieu, co-existing
medical conditions, such as diabetes mellitus, etc.
18F-FDG acquisition parameters. The
acquisition parameters for 18F-FDG cardiac scans are similar to
those used for myocardial viability. Because a majority of
these individuals also have cardiac devices, when hybrid
PET/CT imaging is used, focal hot spots may be noted
corresponding to the device leads. For this reason, both
attenuation-corrected and non-attenuation-corrected images
are reconstructed. Whenever feasible, a hybrid PET/CT scan
may be preferable compared to a dedicated PET scan to
localize region of 18F-FDG uptake.
Dose. Typically, about 8 to 10 mCi of 18F-FDG is
injected intravenously into a peripheral vein manually or
using an automatic injection system. Use of an automatic
injection system (1 mL/s) may significantly reduce
occupational radiation exposure to the technologists.139
The height and weight of the patient and the preinjection
and the post-injection doses (subtracting residual activity)
are logged into the acquisition computer. This
information is critical for estimating standardized radiotracer
uptake values. It is important to keep the dose,
injectionto-scan time, method of radiotracer dose (with or without
residual subtraction), and the acquisition parameters
similar for any follow-up scans.
Scan start time and duration. 18F-FDG
imaging is started 90 minutes (minimum of 60 minutes) after
injection of radiotracer to allow for accumulation of
radiotracer in the inflamed tissue. The acquisition
includes a partial whole-body scan to include the lungs
and mediastinum (3 minutes per bed position for 3D
imaging, and 4 minutes per bed position for 2D scans)
followed by a dedicated cardiac scan (10 minutes per
bed position for 3D, 20 to 30 minutes for 2D imaging).
The whole-body scan is repeated at follow-up.
Image interpretation of cardiac
inflammation: sarcoidosis. As with viability studies, an
accompanying MPI study, preferably with a PET tracer,
such as 82Rb or 13N-ammonia, is important and
considered essential by most practitioners. If a SPECT tracer is
used for perfusion imaging, attenuation correction
should be performed. Perfusion and 18F-FDG slices
should be displayed side by side using a conventional
cardiac display, i.e., standard short-axis, horizontal
longaxis, and vertical long-axis views. A semiquantitative
scoring system, such as that used for perfusion and
viability studies, can be employed. 18F-FDG ‘‘hot
spots’’ identify areas of abnormal cardiac inflammation,
as opposed to ‘‘cold spots,’’ which identify
abnormalities of perfusion or metabolic viability.
Several methods of image interpretation pattern
classification have been described, but none of these are
formally established or validated with histological
findings. One method focuses on 18F-FDG uptake, and
classifies findings as no uptake, diffuse uptake, focal
uptake, and focal-on-diffuse uptake. Another
incorporates perfusion and 18F-FDG information, and classifies
as normal perfusion and normal (i.e., absent) 18F-FDG,
either abnormal perfusion or abnormal 18F-FDG, and
both abnormal perfusion and abnormal 18F-FDG.140 Yet
another group has classified in terms of perfusion and
FDG patterns.141 These classification schemes can help
not only with initial diagnosis, but also to follow up
disease progression and response to therapy.
Observation of 18F-FDG limited to the cardiac
blood pool suggests proper preparation and more
confidently rules out active cardiac sarcoidosis. On the other
hand, diffuse homogeneous cardiac uptake of 18F-FDG,
particularly in the absence of defects on accompanying
perfusion imaging, may indicate inadequate suppression
of cardiomyocyte 18F-FDG uptake and may lead to a
As with metabolic images, interpretation of images for
the presence of active sarcoidosis inflammation must
consider clinical data that might confound image findings.
An important caveat to consider is some of the
aforementioned patterns, such as regions with perfusion abnormalities
that have increased 18F-FDG uptake, could potentially
indicate myocardial hibernation in the setting of ischemic
heart disease. Thus, a diagnosis of active cardiac sarcoidosis
may be difficult, if not impossible, in patients who also have
coronary disease with ongoing ischemia.
Another issue is how to interpret diffuse 18F-FDG
uptake, which may be a consequence of poor dietary
preparation. A focal-on-diffuse pattern suggests disease,
having been reported in about 31% of patients with
sarcoidosis.142 On the other hand, focal 18F-FDG uptake
in the lateral wall and a diffuse basal pattern have been
observed in healthy humans.143
It is also important to recognize that in this type of
study, cardiac 18F-FDG uptake indicates inflammation,
which, while consistent with active sarcoidosis, can also
be caused by a variety of inflammatory disease processes
other than sarcoidosis. This concept needs to be
indicated in the report. Findings may be ‘‘consistent with’’
but are never diagnostic of cardiac sarcoidosis, as tissue
is required for diagnostic certainty.
Image interpretation may be enhanced by
quantifying 18F-FDG uptake using an SUV within each segment
of the heart. SUVs represent the decay-corrected uptake
in the tissue divided by the injected dose of tracer adjusted
for body weight.144 A maximal SUV greater than mean
values plus two standard deviations from control patients
have been suggested as an abnormal threshold,141 with
one report describing a sensitivity of 85% and a
specificity of 90% in reference to JMHW criteria.132 SUV
values have been shown potentially useful in following
patient response to therapy, having been shown to be
associated with response to immunosuppressive
therapy145 and improvement in LV function.146 A coefficient
of variation of regional myocardial SUV, which
represents 18F-FDG uptake heterogeneity, may also help
increase diagnostic accuracy, with a value [0.18 in one
study demonstrating a sensitivity of 100% and a
specificity of 97%, with a decrease in coefficient of variance
seen after corticosteroid therapy.124
A whole-body 18F-FDG PET, as well as CT
transmission image (for hybrid scanning), should also be reviewed
and reported for evidence of extra-cardiac sarcoid disease
activity. Non-cardiac areas of 18F-FDG uptake are
potentially accessible biopsy sites for a definitive diagnosis of
sarcoidosis. Whole-body scans can also provide a ratio of
cardiac 18F-FDG uptake to other regions, such as liver,
cerebellum, and blood pool that may assist in diagnosing
cardiac sarcoidosis and following response to therapy.
Use of cardiac implantable electronic devices
(CIEDs), including pacemakers, cardiac
resynchronization therapy devices, and implantable cardiac
defibrillators (ICDs), as well as left ventricular assist
devices (LVADs), and prostheses, such as valves and
annular ring implants, have become key aspects of
cardiac care. Despite well-established benefits in
appropriate situations, there is a risk of device infection that
has been increasing, with a reported CIED infection rate
of 1.9/1000 device-years and associated blood stream
infection or device-related endocarditis at 1.14/1000
device-years.147,148 There are both intravascular and
extravascular components, and infection can involve the
generator, device leads, or native cardiac structures.148
Device infection carries a high risk of death if not
identified and treated appropriately.149 While
transesophageal echocardiography is customarily the initial
diagnostic approach, imaging of localized inflammation
using radionuclide techniques shows potential for
improving diagnostic accuracy.150–156 One approach is to use
white blood cells labeled with indium-111 or 99mTc.
Factors that may limit the sensitivity of a radio-labeled
white blood cell scan include the viability of the white
blood cells after in vitro labeling process and the migration
rate of the cells to the infection site. The latter becomes a
particular concern in patients who are on antibiotic
treatment, in whom cell chemotaxis is decreased. In
addition, this technique can be cumbersome and costly,
and images are often count-poor with low spatial
resolution. Different from radio-labeled white blood cell
scintigraphy, 18F-FDG PET/CT imaging is based on
in vivo 18F-FDG labeling of the pre-existing inflammatory
cells at the infection site. With the stimulation of cytokines,
these cells (macrophages, neutrophils, and lymphocytes)
overexpress the glucose transporter-1 and accumulate
18FFDG with high concentration.150 Thus, 18F-FDG PET/CT
for in vivo labeling of metabolically active inflammatory
cells at the infection site has the advantage of superior
tomographic images with higher spatial and contrast
resolution, being less labor intensive, and giving less
radiation exposure. 18F-FDG PET/CT can accurately
diagnose infection and, for devices such as an ICD or
pacemaker, may help distinguish deep pocket from
superficial infections.150–152 Lead infection can sometimes also
be identified, but is less diagnostically reliable.
Use of 18F-FDG PET/CT for diagnosing
cardiovascular device infection is based mainly on studies with
relatively small patient cohorts, and needs further
development. Although there are no accepted
interpretation standards at this time, for CIEDs the following are
techniques and issues to consider:152
1. Proper dietary preparation, as described in the prior
sarcoidosis section, is to avoid confusing myocardial
uptake from radiotracer activity in devices or
prostheses next to or within the heart. Patients should
avoid carbohydrates in the meal for 24 hours before
the test and then fast overnight.
2. Both CT attenuation-corrected and non-attenuation
corrected images should be reviewed to help
recognize artifacts of increased tracer uptake related to the
high-density metal in devices. Any ‘‘positive’’
18FFDG uptake on attenuation-corrected images should
be confirmed on non-attenuation-corrected images.
3. Sites of abnormal 18F-FDG PET/CT uptake should be
noted as well as sites of maximal uptake.
4. Site of abnormal uptake should be separated by areas: skin (superficial), subcutaneous tissue, region surrounding the generator, overlying leads, and intravascular/intracardiac.
A qualitative visual score can be used:
5. Fused PET/CT images can be used to provide
anatomic location for tracer uptake sites in relation
to device components, i.e., generator, leads. The
anatomic overlay can help distinguish device from
superficial skin infection.
6. Distribution and pattern of tracer uptake may be more
important than intensity of uptake. Focal or
heterogeneous uptake favors infection, while mild diffuse
uptake along a device or lead may favor non-specific
Regarding PET/CT imaging for LVAD-associated
infections, the literature is sparse, consisting of case
reports.152 Infection can be identified on and around the
pump, and along drivelines and cannula; however,
specific criteria for image interpretation have not been
Diagnosis of prosthetic valve endocarditis is
challenging. While customarily echocardiographic techniques and
blood cultures are the major criteria for making the
diagnosis, each of these has limitations. 18F-FDG PET/
CT can facilitate the diagnosis of prosthetic valve
endocarditis increasing sensitivity from 70% to 97% in relation
to the modified Duke criteria, without decreasing
specificity.107,153 The following are issues to consider when
performing and interpreting 18F-FDG PET/CT imaging for
suspected prosthetic valve endocarditis:
• Inflammatory activity may cause false-positive
18FFDG PET/CT results, such as early after prosthetic
• Surgical adhesive used to seal an aortic root graft may
produce inflammation resulting in false-positive tracer
• Small vegetations may cause false-negative results.
• Physiologic myocardial uptake of 18F-FDG PET/CT
and cardiac motion can interfere with proper image
Currently, 18F-FDG PET/CT imaging is not
considered an initial or confirmatory study for prosthetic
valve endocarditis.155 At this time, the technique
appears most useful for patients with suspicion of
endocarditis but with indeterminate or negative clinical,
echocardiographic, or microbiological findings.
REPORTING OF MYOCARDIAL PERFUSION AND
METABOLISM PET STUDIES
The report should start with the date of the study,
patient’s age, sex, height, and weight or body surface
area, as well as the patient’s medical identification
Indication for Study
Understanding the reason(s) why the study was
requested helps in focusing the study interpretation on
the clinical question asked by the referring clinician. In
addition, a clear statement for the indication of the study
has become an important component of billing for
services rendered. For sarcoidosis and infection studies,
list prior clinical findings or correlative imaging results
that led to consideration of the 18F-FDG PET scan.
History and Key Clinical Findings
A brief description of the patient’s clinical history
and findings can contribute to a more appropriate and
comprehensive interpretation of the rest (and stress)
perfusion and of the metabolism images. This
information may include past myocardial infarctions and their
location, revascularization procedures, the patient’s
angina-related and congestive heart failure-related
symptoms, presence of diabetes or hypertension, and
other coronary risk factors. Information on regional and
global LV function can similarly be important for the
interpretation of regional perfusion and metabolism
A description of the ECG findings may serve as an
aid in the study interpretation, such as the presence of
Qwaves and their location or conduction abnormalities
(e.g., LBBB) for exploring septal perfusion and/or
metabolic abnormalities. A list of current cardiac
medications should be included. For sarcoidosis and
cardiovascular infection studies, identify if this is the
initial study or follow-up study and list current
immunosuppressive and infection therapy, respectively.
Type of Study
The imaging protocols should be stated concisely.
This should include the type of camera utilized for
imaging myocardial perfusion and/or metabolism, for
example, PET or PET/CT system, or SPECT perfusion
and 18F-FDG PET metabolism. For stress myocardial
perfusion PET studies, the type of stressor should be
clearly indicated, such as treadmill, dipyridamole,
adenosine, regadenoson (A2A adenosine receptor agonist), or
dobutamine. Radiopharmaceuticals and their
radioactivity doses used for the perfusion and the metabolism PET
imaging studies should be identified. The acquisition
modes and image sequences should be described, such as
static or dynamic image acquisition, for stress and rest
perfusion imaging, perfusion and metabolism imaging on
different days, and the use of gating.
The main body of the report following this
introductory descriptive information should then be tailored
to the specific clinical question asked by the referring
clinician and the procedural approach chosen for
answering this question.
Summary of Stress Data
If myocardial perfusion has been evaluated during
stress, the type of the stressor, the stress agent, the dose,
route of administration, and time of infusion should be
specified. Side effects and symptoms experienced during
stress should be reported. If pharmacologic stress was
discontinued prematurely, the reasons should be
Hemodynamic and ECG responses during the stress
study, including changes in heart rate, blood pressure,
development of arrhythmias, conduction abnormalities,
and ST-T wave changes and their location, should be
detailed. Symptoms such as chest pain, shortness of
breath, and others during the administration of the stressor
and in the recovery phase should be documented.
Information about the dietary state (e.g., fasting or
postprandial) and about interventions for manipulating
plasma glucose levels through, for example, oral or IV
administration of glucose or use of the
euglycemichyperinsulinemic clamp, should be given. If
pharmacologic measures, such as nicotinic acid derivatives, have
been used, this should be described. Furthermore, blood
glucose levels, if obtained at baseline or after intervention,
should be listed, as they are useful for the interpretation of
the metabolic images. If there is an expected abnormal
response to a glucose load, this should also be reported.
For sarcoidosis and cardiovascular infection studies,
list the dietary preparation used to suppress glucose
utilization by normal myocardium and the method used
to interpret 18F-FDG uptake (relative or SUV values).
A statement regarding image quality is important.
Reduced quality may affect the accuracy of the
interpretation. If the cause of the reduced quality is known or
suspected, then it should be stated accordingly. This
information may prove useful when repeat images are
obtained in the same patient.
The report should first describe the relative
distribution of the perfusion tracer on the stress images and
provide details on regions with decreased radiotracer
uptake in terms of the location, extent, and severity of
defects that may be supplemented by a diagram. The
authors should then describe whether regional
myocardial defects seen on stress images become reversible or
persist on the corresponding paired rest images. Other
findings, such as LV cavity dilatation at rest, transient
(stress-induced) LV cavity dilatation, lung uptake,
concentric LV hypertrophy, asymmetric septal
hypertrophy, pericardial photopenia, prominent RV cavity
size and hypertrophy, and extra-cardiac abnormalities,
should be included in the report. Regional and global LV
function should be described from gated PET perfusion
and/or metabolism images. The scintigraphic pattern on
the stress/rest myocardial perfusion images should then
be reported in clinical terms as:
3. Fixed defect. This should be considered scarred if
there is a history of prior myocardial infarction or
pathologic Q-waves on the ECG. However, in the
absence of prior myocardial infarction or ECG
Qwaves, particularly in patients with new-onset heart
failure, hibernating but viable myocardium should be
considered and assessed with additional myocardial
4. An admixture of scarred and ischemic but viable myocardium.
5. Non-ischemic cardiomyopathy. Quantitative assessment of absolute regional MBF can be presented as an adjunct to the visual interpretation in the proper patient population.
Image Description and Interpretation:
Metabolism for Myocardial Viability,
Sarcoidosis, and Cardiovascular Infection
18F-FDG myocardial viability study. The
report should describe the relative distribution of
myocardial perfusion at rest, and the location, extent,
and severity of regional perfusion defects. The report
should continue with a description of the 18F-FDG
uptake in the myocardium and indicate the tracer
activity concentrations in normally perfused and in
hypoperfused myocardium. The adequacy of achieving a
glucose-loaded state, as evident from the radiotracer
uptake in normally perfused myocardium and also from
blood pool activity, should then be reported and be
related to the presence of insulin resistance, including
impaired glucose tolerance and type 2 diabetes. This
should be related to the residual blood pool activity as
additional evidence for inadequate clearance of
18FFDG from blood into tissue and provide the information
for low tracer uptake in normally perfused myocardium.
Segments with regional dysfunction that exhibit patterns
of viable myocardium (i.e., preserved perfusion or
decreased perfusion with relatively increased 18F-FDG
uptake) should be identified. Similar reporting should be
performed for segments exhibiting a flow-metabolism
matched pattern, that is, decreased regional 18F-FDG
uptake in proportion to decreased regional myocardial
perfusion. The presence of viable and non-viable tissue
should be reported as a continuum (e.g., predominantly
viable or admixture of viable and non-viable tissues).
Findings on semiquantitative or quantitative image
analysis, supplemented by a diagrammatic approach,
may be added. Location and, in particular, extent of
viable and non-viable tissues, expressed as a percentage
of the LV, is important because it provides important
prognostic information on future cardiac events
and predictive information on potential outcomes in
regional and global LV function, congestive heart
failure-related symptoms, and long-term survival after
revascularization. Finally, the description of the
perfusion-metabolism findings may include a correlation to
regional wall motion abnormalities and should indicate
the potential for a post-revascularization improvement
in the regional and global LV function. The potential for
outcome benefit may also be reported.
18F-FDG sarcoidosis/infection study. A
statement regarding image quality and adequacy of
suppression of glucose utilization by normal
myocardium is important. Incomplete suppression of glucose
utilization by normal myocardium may reduce the
accuracy of the interpretation.
For sarcoidosis and infection 18F-FDG studies
wherein whole-body images are obtained, the
wholebody 18F-FDG findings should be reported. Sarcoidosis
is a systemic disease and systemic disease activity may
be important for management. Regions of abnormal
18FFDG uptake that may be accessible for biopsy should be
reported. For infection studies, if distal septic
embolization sites are identified, they should be reported.
Final interpretation. Results should be
succinctly summarized and first addressed whether the
study is normal or abnormal. On rare occasions where a
definitive conclusion cannot be made, the interpreter
should aid the referring clinician by suggesting other
tests that may provide further insight into the clinical
dilemma. The report should always take into
consideration the clinical question that is being asked: is the study
requested for CAD detection or myocardial viability
assessment? Any potential confounding artifacts or other
quality concerns that significantly impact the clinical
interpretation of the PET study should be mentioned.
A statement on the extent and severity of perfusion
defects, reversibility and mismatch in relation to 18F-FDG
metabolism, and their implication regarding ischemia,
scar, or hibernating myocardium should be made. It may
be useful to conclude the report with a summary of the
extent and location of myocardial ischemia in relation to
vascular territories, as well as the presence and extent of
perfusion-metabolism mismatch in patients with chronic
ischemic LV dysfunction. LV cavity size, function, and
regional wall motion should be reported at rest and during
stress with special note of transient ischemic cavity
dilatation, if present. A statement as to the implication of
the findings should be made.
Comparison should be made to prior studies, and
interim changes regarding the presence and extent of
myocardial ischemia, scar, or hibernation should be
highlighted. On the basis of the scintigraphic findings
(e.g., extent of perfusion-metabolism mismatch), the
likelihood of recovery of function after revascularization can
be estimated. The potential for a post- revascularization
improvement in contractile function is low for
perfusionmetabolism matched defects, even if the regional
reductions in perfusion and in 18F-FDG uptake are only mild or
moderate. Conversely, the potential for improvements in
regional contractile dysfunction is high if perfusion is
normal, if both perfusion and 18F-FDG uptake are normal,
or if 18F-FDG uptake is significantly greater than regional
perfusion (i.e., mismatch). Finally, the potential of a
postrevascularization improvement in the LVEF by at least 5 or
more EF units is high if the mismatch affects 20% or more
of the LV myocardium,108,156 although lesser amounts of
mismatch (5 to 20% of the LV myocardium) may also have
potential outcome benefit, with or without improvement in
the LVEF.157,158 The latter may be included in the report at
the reporting physician’s discretion.
For sarcoidosis and infection studies which are hot
spot images, comparison to prior studies is based on SUV
values or ratio of relative uptake in relation to another
organ. Changes in response to therapy are indicated as
changes in SUV. Comparison to prior studies, cardiac
MR or echocardiography, when available may be helpful.
If additional diagnostic clarification seems to be
needed, the physician may recommend an alternative
modality. If a CT transmission scan was performed for
attenuation correction, clinically relevant CT findings
must be reported.
Dr. Rob S. Beanlands is a consultant to Lantheus Medical
Imaging and Jubilant DRAXImage and receives grant support
from Lantheus Medical Imaging, Jubilant DRAXImage, and
GE Healthcare; Dr. Robert J. Gropler is a consultant to
Biomedical Systems; Dr. Juhani Knuuti is a consultant to
Lantheus Medical Imaging and serves on the speakers bureaus
of GE Healthcare and Philips. All other contributors have
nothing relevant to disclose.
APPENDIX: SAMPLE IV PROTOCOL
A sample protocol for IV glucose loading, based on
one in use at Vanderbilt University Medical Center,
Nashville, TN, and adapted from Martin et al58 is
1. IV glucose/insulin loading for non-diabetic patients
with a blood glucose (BG) level \110mg/dL (\6.11
mmol/L) under fasting condition.
a. Prepare dextrose/insulin solution: 15 U of regular
insulin in 500 mL of 20% dextrose in a glass
bottle. The initial 50 mL is discarded through the
plastic IV tubing (no filter) to decrease adsorption
of the insulin to the tubing.
b. Prime the patient with 5 U of regular insulin and
50 mL of 20% dextrose (10g) IV bolus.
c. Infuse dextrose/insulin solution at a rate of 3 mL
kg-1 h-1 for 60 minutes (corresponding to an
insulin infusion of 1.5 mU kg-1 min-1 and a
glucose infusion of 10 mg kg-1 min-1). Monitor
BG every 10 minutes (goal BG, 100 to 200 mg/dL
[5.56 to 11.11 mmol/L]).
d. If BG at 20 min is 100-200 mg/dL (5.56 to 11.11
mmol/L), preferably \150 mg/dL (8.33 mmol/L),
administer 18F-FDG intravenously.
e. If BG is [200 mg/dL ([11.11 mmol/L),
administer small IV boluses of 4 to 8 U of regular insulin
until BG decreased to \200 mg/dL (\11.11
mmol/L). Administer 18F-FDG intravenously.
f. Stop dextrose/insulin infusion at 60 minutes and
start 20% dextrose at 2 to 3 mL kg-1 h-1.
g. During image acquisition, continue infusion of
20% dextrose at 2 to 3 mL kg-1 h-1.
h. At completion of the acquisition of the images,
discontinue infusion, give a snack to the patient,
and advise him or her regarding the risk of late
(i) If BG is [400 mg/dL ([22.22 mmol/L), call
the supervising physician immediately.
(ii) If BG is \55 mg/dL (\3.06 mmol/L) or if the
patient develops symptoms of hypoglycemia
with BG \ 75 mg/dL (\4.17 mmol/L),
discontinue dextrose/insulin infusion,
administer one amp of 50% dextrose intravenously,
and call the supervising physician.
2. IV glucose/insulin loading for diabetic patients or
fasting BG is [110 mg/dL ([6.11 mmol/L):
a. Prepare insulin solution: 100 U of regular insulin
in 500 mL of normal saline solution in a glass
bottle. The initial 50 mL is discarded through the
plastic IV tubing (no filter) to decrease adsorption
of the insulin to the tubing.
b. Prime patient with regular insulin: If fasting BG is
[140 mg/dL ([7.76 mmol/L), prime the patient
with 10 U of regular insulin IV bolus. If fasting
BG is \140 mg/dL (\7.76 mmol/L), prime the
patient with 6 U of regular insulin IV bolus.
c. Infuse insulin solution at a rate of 1.2 mL kg-1
h-1 for 60 minutes (corresponding to an insulin
infusion of 4 mU kg-1 min-1) or for the entire
study (to calculate the regional glucose utilization
d. After 8-10 minutes or when BG is \140 mg/dL
(\7.76 mmol/L), start 20% dextrose infusion at
1.8 mL kg-1 h-1 (corresponding to a dextrose
infusion of 6 mg kg-1 min-1).
e. Monitor BG every 5 to 10 minutes and adjust
dextrose infusion rate to maintain BG at 80 to 140
mg/dL (4.44 to 7.76 mmol/L).
f. After 20 to 30 minutes of stable BG, administer
g. Maintain the IV infusion of insulin plus 20%
dextrose for 30 to 40 minutes after 18F-FDG
injection or until the end of the scan (to calculate
rMGU [rate of glucose utilization]). Some centers
confirm 18F-FDG uptake particularly in patients
with diabetes before discontinuing the clamp.
h. At completion of the acquisition of the images,
discontinue infusion, give a snack to the patient,
and advise him or her regarding the risk of late
3. For lean patients with type 1 juvenile-onset diabetes mellitus, apply the following protocol:
a. If fasting BG is \140 mg/dL (\7.76 mmol/L),
inject 4 U of regular insulin and infuse insulin
solution at 0.3 mL kg-1 h-1 (1 mU kg-1 min-1).
b. After 8-10 minutes of infusion or when BG is
\140 mg/dL (\7.76 mmol/L), start 20% dextrose
at 2.4 mL kg-1 h-1 (8 mg kg-1 min-1).
4. Some centers (Munich, Ottawa, and others) have also
applied a front-loaded infusion.
a. About 6 hours after a light breakfast and their
usual dose of insulin or oral hypoglycemic, all
diabetic patients have a catheter inserted in one
arm for glucose and insulin infusion, as well as a
catheter in the opposite arm for BG measurement.
b. At time 0, the insulin infusion is started. Regular
insulin is given at 4 times the final constant rate
for 4 minutes, then at two times the final constant
rate for 3 minutes, and at a constant rate for the
remainder of the study.
c. If the BG is [200 mg/dL ([11.11 mmol/L), an
additional bolus of insulin is given. An exogenous
20% glucose infusion is started at an initial rate of
0.25 mg kg-1 min-1 and adjusted until stead state
is achieved. The BG concentrations are measured
every 5 minutes during the insulin clamp. The
glucose infusion is adjusted according to the
plasma glucose over the preceding 5 minutes.
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