Comparison of both PET and CT raw and reconstructed file sizes
Combined and optimized Positron Emission Tomography and Computed Tomography (PET-CT) exams are among the more complex of the radiographic modalities utilized in both body oncology and neurology settings. A distinct and targeted workflow is essential to successful data acquisition, processing, and related image management and reporting [1, 2]. This chapter will review the primary considerations involved in acquisition, processing, and archiving of PET-CT raw data and image data in a clinical PET-CT environment primarily centered on oncology and neurology.
2. Raw data acquisition
The method utilized for the creation of PET images is steeped in proprietary acquisition techniques available from a very limited number of PET-CT scanner manufacturers. Regardless of the manufacturer, successful PET-CT acquisition depends on a consistent quality assurance and quality control program as well as an attentive technologist staff and supportive physicist. Routine and careful quality control at daily intervals is at the center of any high performing PET-CT department. The pinnacle of PET quality control is the acquisition and evaluation of PET sinograms that comprise the raw data. PET-CT raw data consists of gigabyte sinogram data sets that are used to generate image sets consisting of transverse slices. Each transverse slice maps to a sine wave frequency. These frequencies on the sinogram can be practically visualized as displacements or rows on the x axis and an angle on the y-axis which represent a projection through the object being imaged. At the smallest level, each pixel in the sinogram corresponds to specific line-of-response (LOR) based on the byproducts of a positron annihilation event detected in the scanner PET crystals. The resulting pixel rendering is considered image data. Additional or revised reconstructions of different slice thickness or overlap can only be rendered from
The PET sinogram will reveal excessive and non-uniform fluctuations occurring in the gantry crystal detector architecture. Any significant change in the detector crystals will be manifest as a “stripe” of non-uniformity. In most cases, this stripe indicates a detector block failure. The presence of a failed detector block will require a repeat of the quality control to attempt to verify scanner malfunction. Block failure is a serious malfunction that in most cases requires the intervention of a PET service engineer. The block will either need to have the corresponding electronics tuned or the block will require replacement in order to continue with scanning. Figure 2 depicts a PET sinogram with a failed block artifact.
PET scintillation crystals are especially susceptible to failure due to environmental conditions such as dramatic alterations in ambient temperature, humidity, or cooling infrastructure. As a result, the technologist should intermittently but frequently review a gantry interface that provides a continuous report of gantry status and conditions. In particular, the technologist should be mindful of alterations in gantry temperature or dew point as well as substantial changes in the voltage of the detector electronics. Maintaining vigilance in monitoring gantry conditions can be an important part of early troubleshooting to minimize delays and eventual downtime. Figure 3 demonstrates a typical positron emission tomography acquisition interface.
3. Raw data reconstruction into processed image data
Once an appropriate sinogram data set has been acquired and confirmed as meeting the manufacturer and site-specific quality control requirements, reconstruction of slices from the data can be commenced. Common and clinically useful reconstructions include filtered back projection corrected and uncorrected images as well as iterative reconstructions. With iterative reconstructions, manufacturers are also bringing to bear time of flight capabilities made possible as a result of the very latest and most progressive reconstruction algorithms. Regardless of the vendor or reconstruction methodology employed, any actions necessary to correct for random events, scatter, decay, normalization, and dead time will be applied.
Two dimensional (2D) versus three dimensional (3D)acquisitions continue to play a role in image reconstruction management with 3D gaining primacy and near routine usage for all PET reconstructions . In the earlier days of PET, 2D imaging was the most desirable and feasible means of imaging. This was true because, too many events would be detected within the PET crystal array with excessive dead time and image degradation in adjacent PET detector rings. This was overcome by placing septa comprised of tungsten or lead in between the detector rings. Along with these septa, the scanner electronics were configured to only detect coincidence events from within a limited plane to exclude non-collinear events. This also reduced the sensitivity of coincidence detection and corresponding image resolution. With improvements in crystal technology and detector electronics, it became possible to remove the septa that separated PET rings and detect collinear events in the adjacent PET rings. This could occur without concomitant dead time affects and allowed for a nearly quadruple increase in sensitivity. Figure 4 depicts 2D mode imaging (left) and 3D mode (right):
Attenuation corrections methods must also be implemented routinely or the PET axial images will have a muted or dim appearance for those structures that are more towards the center and deeper aspects of the patient’s anatomy. The most simple attenuation correction method is that of filtered back projection whereby the body is assumed to be an ellipse of relatively uniform density. This “Chang technique” works well in uniformly dense anatomic structures but is woefully slow and inadequate in portions of the anatomy that contains variable density structures. Therefore, for both speed and accuracy, measured attenuation is preferable via the use a of a CT source. The historical arc of PET-CT attenuation projection has progressed from usage of an external transmission rod source to “modern” CT scanners that are now commercially available and integrated with PET-CT. CT detector architecture utilizing upwards of 128 rows can now be found on commercially available PET-CT scanners . In the earlier days of PET, Ge-68 or Cs-137 rod sources were used to generate a transmission scan through each slice of the patient’s body resulting in a measurement of attenuation correction for each pixel. Typically, the rod source was maintained within a shielded portion of the gantry. Upon the issuing of a transmission command from the scanner operating software, the shielded rod would be extended and rotated about the patient for a predefined time per bed position, usually 3-4 minutes per bed. This was a lengthy process that commonly took upwards of 30 minutes to complete. Modern PET scanners no longer utilize transmission rod sources and PET scanners containing CT infrastructure are the norm due to the dramatically increased speed of acquisition and resulting attenuation correction map . Figure 5 depicts transmission scan created with a rotating radioactive rod source assembly.
The advantage of the traditional transmission rod source was that the patient received much less radiation dose with a transmission rod source compared to modern CT transmission methods . Additionally, the transmission data were acquired in the native 511 keV energy obviating the need for segmentation that is required for CT. Segmentation involves smoothing the transaxial CT images to approximate the spatial resolution of the PET scanner. This segmentation is necessary because the energy settings of 80-140 keV inherent to CT are much lower than the 511 keV energies common to PET. The pixel values of these regions are altered and replaced with the known linear attenuation coefficient for the imaged tissue or other internal materials such as a prosthetic (joint replacement, pacemaker etc.). The process of replacing the pixel values eliminates a considerable amount of noise inherent in the “raw” image. The segmented CT attenuation map is scaled to the 511 keV and applied as attenuation correction to the PET images.
As mentioned previously, the PET-CT scanning acquisition results in the creation of raw projection data. This raw projection data is processed and rendered into reconstructed image sets. It is common practice at most clinical imaging institutions to retain the CT raw projection data for a limited number of days. This permits sufficient time to elapse such that the corresponding reconstructed images can be reviewed by the interpreting physician. It is particularly important to retain the raw data for those limited but important circumstances that the interpreting physician requests an additional reconstruction for better elucidation of a particular abnormality prior to generating the final scan interpretation. Reconstructed axial images may also be utilized to create additional projections including coronal and sagittal image sets. If the images are to be used outside of the oncology realm that PET-CT has principally been concerned with, the image data will be rendered into vertical and horizontal long axis images to accompany the usual transverse/transaxial image sets. However, certain institutions due to internal protocols or to adhere to specific research protocols must retain the raw data indefinitely. In this case, a reliable and timely means of archiving of all of the raw data generated by a scan will be necessary. There are myriad options available for archiving of said data. Reliable and timely archiving and retrievabililty will figure prominently in deciding which type of archiving solution is appropriate. Despite the increasing availability of robust and inexpensive computer memory, these data sets quickly deplete available hard drive space and create a pressing need for removal. This is because the CT raw data sets are much larger when compared to a corresponding PET acquisition of the same axial coverage. Archival and retrieval methods and strategies will be covered later in this chapter.
The amount of raw image data space required for each PET-CT examination depends on both the particular scanner configuration as well as the scan protocols in general usage by a facility. Each PET bed will require fewer than 10 megabytes (MB) of storage for lower matrix acquisitions. Lower matrices are usually those that are lower than 256. A lower matrix would be commonly used for axial coverage necessary for torso-based oncology such as breast, colorectal, and lymphoma staging and restaging. Higher matrices, such as those used for head & neck oncology or neurology imaging on the very latest and modern PET-CT scanners, are as high as 512. These high, fine matrices will require in excess of 70 MB for a single PET bed position. Figure 6 shows lower and higher matrix image examples.
CT raw data requires substantially more space, with modern 64-row scanner used in PET-CT generating upwards of 70 MB of projection data per second. As a result, the typical whole torso PET-CT examination can readily require in excess of 2 gigabytes (GB) of hard drive storage space for the raw data alone when there is a single CT acquisition created for the entire torso axial coverage (Table 1). With the addition of other CT acquisitions which may include lung breath hold, multiple contrast phases or longer axial coverage, the raw data space consumed increases accordingly to 4 GB and greater. The reconstructed images consume considerably less hard drive space; an entire image set, including different PET and CT image reconstructions occupy less than 500 MB. Common PET image reconstructions include attenuation corrected iterative and non-attenuation corrected filtered back projection. Figure 7 depicts the transaxial PET reconstructions commonly used in body oncology imaging.
In a very active practice in which 10 or more patients are imaged per scanner, several GB of hard drive space can be easily filled in the course of a day . If the PET-CT technologist does not routinely transfer raw data sets and reconstructed image sets to other storage sites or delete them from the hard drive space on a routine basis, system functionality can be severely hampered. In some cases, intensive hard drive utilization may cause database corruption resulting in significant interruptions and possibly downtime. Table 1 depicts a comparison of both PET and CT raw and reconstructed file sizes.
|File size assumptions: A PET bed occupying approximately 10 cm of axial coverage requires 70 MB. A CT of the corresponding PET axial coverage is 3 times as large or ~ 210 MB. *The typical PET-CT would be of the torso ("skull base to thighs") and would be approximately 5-6 bed positions. Depending on the axial field of view, wholebody (skull vertex to toes) imaging may require as many as 15 or more bed positions to provide sufficient axial coverage.|
Common and scalable raw and image data archiving strategies and solutions will be discussed later in this chapter.
4. Time-of-flight PET
The PET scanner crystals remain the primary limiting factor in both image resolution and speed of acquisition capabilities . The development and implementation of Time-of-Flight (ToF) technology has been the primary strategy targeted at improving image resolution and acquisition speed [8, 9]. The concept of time of flight dates back many years and was utilized for limited applications employing very fast and expensive crystal arrays [8, 9]. The economics of crystal manufacture combined with more affordable and rapid computer processors and memory have made ToF feasible to deploy among virtually all of the mainstream PET-CT manufacturers. The crystal standard for many years in PET technology was the bismuth germinate crystal. It had the advantage of having good 511 keV stopping power, universal availability and was well-tested within PET gantry design. However, it lacked the fast scintillation capabilities that are essential to ToF PET. Lutetium oxyorthosilicate (LSO) or cerium-doped lutetium yttrium orthosilicate (LYSO) have emerged as the industry standard capable of the rapid scintillation times necessary to support ToF .
The principle advantage of ToF is the ability to dramatically improve the positioning of annihilation events that occur outside of the line of response (LOR). This is accomplished by locating the annihilation photon energy deposition on the opposing sides of the ring of crystals in the PET gantry and determining the difference in arrival times of those events.
It is important to understand that ToF allows for better lesion detectability not because of improvement in resolution but as a result of improved signal-to-noise definition inherent in improved timing resolution. For this to occur in contemporary PET scanners, the coincidence timing window must be configured to be very short (4-6 nanoseconds) to improve the fraction of randoms detected and resultant improvement in image contrast.
5. Quantitative PET imaging: Considerations for optimizing and rendering the standardized uptake value (SUV)
Provided accurate attenuation correction is performed, PET scanners provide the opportunity to generate semi-quantitative measurements of tumor metabolism. These measurements, known as standardized uptake values (SUVs) continue to be the primary and most universally accepted method for generating semi-quantitative measurements that depict tumor metabolism . The default unit of measurement in all PET scanners is kilobecuerels per milliliter. This unit of measurement together with the quantity of injected radioactivity, patient weight, and decay time is used to compute the SUV. Considerable error inherent to all of the aforementioned criteria can result in badly flawed measurements and ultimately, false tumor metabolism quantification. In order to reduce the likelihood of introducing error in SUVs, at a minimum, the following must be evaluated and effectively implemented in the SUV calculation :
Scanner cross-calibration: procedure performed to ensure that dose calibrator dose assays match the radioactivity measured by the PET scanner.
Measurement of residual syringe activity: This occurs immediately subsequent to administering the dose to the patient. The residual syringe activity is subtracted and the total quantity administered is recorded in the radiopharmaceutical administration record. This same resulting quantity is used for all SUV calculations.
Synchronization of all clocks utilized in reporting injection time
Assurance of proper infusion of radiopharmaceutical (no dose extravasation)
Accurate patient weight
Accurate patient dose
The equation for SUV calculation is as follows:
Because radiopharmaceutical dose and patient weight are in the denominator, these are among the 2 most important values to optimize to reduce the magnitude of error inherent to the calculation.
6. Computed Tomography acquisitions considerations for PET-CT
Prior to 1998 and the prototype development of the PET-CT at the University of Pittsburgh, PET-only systems had primacy given that those systems were the only offering available . The genesis of PET combined with CT derived from the suggestion of a Swiss oncology surgeon. During the development of the PET-CT, the oncologist opined that a CT scanner in the voids between the banks of the PET detectors might provide useful anatomical information familiar to oncology surgeons. This suggestion was a catalyst to the advent of the modern-day PET-CT. Dr. David Townsend and Ron Nutt began creating a prototype PET-CT in 1991 but it would not be a viable device for use clinically until 1998 .
Since that time, the practice of PET-
There has been considerable divergence over the routine integration of optimized, contrast enhanced CT with PET. However, over the course of the past decade, the literature has repeatedly borne out the superior quality and efficacy of optimized CT used in conjunction with PET [12, 13]. The most strident objection to performing optimized, contrast-enhanced CT with PET is that the oral and/or intravenous contrasts utilized on the CT creates artifacts in the PET images. More specifically, it was proposed that the intravenous contrast or oral barium sulfate attenuation correction artifacts diminished the readability of the PET [14, 15]. While there are limited examples of attenuation correction artifacts from oral or intravenous contrast, experienced PET-CT readers have learned to utilize filtered back projection uncorrected images to differentiate artifacts versus clinically relevant findings . The emergence of routinely used dual syringe intravenous contrast injectors that permit the injection of a normal saline “chaser” after the initial intravenous contrast have virtually eliminated intravenous contrast artifacts on the attenuation corrected images .
There are substantial requirements and preparations necessary to incorporating optimized CT into PET-CT practice . The most ideal approach has been to have truly-dually trained and boarded radiologists and technologists working together to produce the PET-CT images. Regrettably, this situation is rarely achievable given the time investment necessary to garner nuclear medicine physician and radiologist credentials or for similar circumstances to be available to nuclear medicine technologists. Nevertheless, it is possible to routinely incorporate optimized CT into the PET-CT practice provided there can be collaboration between nuclear medicine and CT departments.
Critical considerations for optimizing CT acquired along with PET include configuring scanner parameters for the best quality image while dosing the patient safely. Technologist staff should become knowledgeable regarding basic CT principles such as pitch and slice overlap, CT dose index (mGy and mAs or mA), slice thickness and noise inter-relationship, and x-ray penetration characteristics (keV setting). Intravenous contrast administration requires careful screening of each patient both at the time the patient’s appointment is scheduled as well as during the actual appointment. Internal protocols should be developed to optimize the patient’s ingestion of oral contrast, administration of intravenous contrast for optimized bolus timing, as well as persistent awareness of the potential for contrast reactions. Figure 8 illustrates a protocol for PET-CT incorporating optimized CT:
A final consideration for performing optimized CT is patient safety given clinically significant findings. In the course of performing optimized CT, it is not uncommon to encounter a large pleural effusion (fluid in the lungs) or a pneumothorax (collapsed region of lung) or similar life-threatening circumstance. PET-CT technologists must be vigilant and trained to routinely evaluate the CT images for obvious significant findings and report these findings to a radiologist for appropriate follow up. Figure 9a illustrates a pleural effusion and Figure 9b shows a pneumothorax:
On rare occasions, pulmonary emboli are also encountered and must be reported but these findings are often extremely subtle even to the experienced imager.
Along with noticing clinically significant findings during and subsequent to the scan, it is vital that the technologist provide the utmost in safety while administering intravenous contrast. The threat of intravenous contrast extravasation, allergic reactions, or renal compromise are the foremost dangers for the patient. It has been well-documented that intravenous contrast extravasations of 100 milliliters or greater almost always require a plastic surgery consult as localized tissue necrosis may occur . This is because the osmolality of commonly used non-ionic intravenous contrast (~650 mOsm/kg) is often vastly different from osmolality of blood (~285 mOsm/kg) creating conditions for unfavorable osmotic gradients to occur . The majority of intravenous contrast extravasations can be avoided entirely by verifying venous patency prior to and during the administration of contrast . Figure 10 demonstrates a graphical depiction of the venous patency both
Additionally, though uncommon, allergic reactions to intravenous contrast range from localized mild urticaria to anaphylactic shock . Also, patients at risk for renal insufficiency such as those who have diabetes, hypertension, solitary kidney, or any combination of the aforementioned are at substantial risk for developing contrast induced nephropathy (CIN) . Therefore,
7. Image fusion
Prior to the introduction and routine utilization of modern PET-CT scanners, the technologist or similar staff used third party programs in post-processing attempts targeted at aligning PET and CT or PET and MR image sets that had been acquired on different scanners. In addition, the radiologist was also tasked with customary mental alignment of image metabolism structures, so called “mental fusion” . The fully integrated and combined PET-CT has allowed for practical and real-time image fusion that is considered commonplace in contemporary imaging . Unfortunately, this has not obviated the need for third party image fusion systems because fusion of IR, MR or other modality fusion is now considered standard-of-care. This is increasingly becoming the case in multidisciplinary oncology environments as well as neurology subspecialty environments that include an epileptologist as part of a multidisciplinary epilepsy team. Until recently, rigid fusion was the only possible fusion option. Rigid fusion involves image landmark matching to achieve the closest best fit among anatomic structures and metabolic activity. This is achievable by using software to co-register multiple image volumes against a reference volume. However, due to myriad alterations in patient position between scanners, patient weight changes, and surgical variants rigid fusion frequently reveals undesirable matches between image sets. In contrast, deformable fusion has emerged and permits more favorable metabolic and structural alignment by incorporating virtual stretch algorithms. This involves mutual information algorithms that function at the pixel and/or voxel level to “warp” the image data .
Provided the processed image matrices are similar, deformable fusion is routinely achievable and permits for favorable and clinically useful alignment of morphological and metabolic image sets across multiple cross-sectional modalities .
8. Workflow and the optimized PET-CT acquisition: The United States perspective
If PET-CT experienced a “golden age” it was immediately following more widespread adoption of PET-CT in the early 2000s. Numerous PET-CT facilities had business models based upon as few as 3 patients per day due to robust reimbursement that prevailed up until 2005. This was an ephemeral but important time of prosperity, growth, and development for PET-CT. At that time, the per scan fee provided by the Centers for Medicare and Medicaid Services (CMS) was at an all time high. This period was destined for an eventual phase out but was hastened by the implementation and enforcement of the Deficit Reduction Act (DRA) [26, 27, 28, 29].The DRA of 2005 (signed into law February of 2006) was implemented as part of a broader strategy targeted at limiting the unnecessary expenditure of funds thought to be redundant in patients’ care . The ultimate result of this policy was that reimbursement for PET-CT was reduced by nearly one half in the non-hospital, free-standing imaging environment . Many independent imaging centers that once prospered by only performing 3 or 4 patients per day no longer could achieve a margin to sustain a solvent business model. In the ensuing aftermath of full phase in of DRA policy, many of these facilities were either assimilated by larger institutions or simply became insolvent and bankrupt.
In addition to the DRA of 2005, a second blow to PET-CT arrived in the form of the major economic downturn and crisis of 2008. This dramatically reduced the borrowing power of institutions as well as the number of patients with healthcare insurance who could afford to have PET-CTs. What emerged was a new paradigm of very efficient, higher volume imaging workflows in PET-CT in both public and private hospital industry. Institutions with targeted and efficient workflows have been able to weather the continued acrimonious economic conditions as funds for both full time equivalents (FTEs) and capital infrastructures such as scanners continues to diminish. PET-CT has continued to grow although the percentage increase has tended to decrease each year since 2005 . This environment is indeed the new normal and will likely persist for several years to come.
9. Specialized acquisition circumstances: Pediatrics, radiation therapy planning, and inpatients
Pediatric PET-CT acquisition requires all of the same precautions as those that accompany adult PET-CT
In any pediatric PET-CT imaging environment, there should be age and weight-specific criteria for dosing the patient with radiopharmaceuticals. One method that can be used is to standardize the pediatric dose to the “standard man” of 70 kilograms while also setting absolute low and high dose limits. As an example, an institution might designate 74 MBq (2 mCi) as the minimum dose and 370 MBq (10 mCi) as the maximum dose. The dose would then be computed with the following equation:
It is helpful to use any number of commercially available spreadsheet programs to extrapolate all values of radiopharmaceutical dosing based on this equation for ease of reference.
Pediatric PET-CT will also require careful consideration of radiation dose delivered in the CT portion of the exam. This is of the utmost importance if the institution has incorporated optimized or diagnostic CT parameters because dose from CT will be nearly twice the radiation dose from the 511 keV emitting radiopharmaceutical such as fluorine-18 2-deoxy-2-fluoro-D-glucose (18FDG) . There are now well-established “Image Gently” protocols available from the American College of Radiology that can assist any facility in creating protocols that provide age-appropriate CT dosing. In recent years, these protocols have become increasingly common in many pediatric-based radiology departments although the adoption of optimized or diagnostic CT parameters in PET-CT has been slower to emerge . Integrated applications to reduce CT dose should be routinely incorporated into the imaging of pediatric patients to maintain their dose as low as reasonably achievable (ALARA). Low dose pediatric CT is generally accepted to be 5 mSv or below for the typical torso axial coverage . This is easily achievable in younger and smaller pediatric patients who possess a lower body mass index (BMI) but becomes considerably more difficult in imaging older and higher BMI pediatric patients. An ongoing and continuing dialogue with a health physicist and radiologist is essential to providing safe and lower dose CT in the pediatric PET-CT environment .
9.2. Radiation therapy planning
Similar to pediatric PET-CT, radiation therapy (RT) planning may be a very small portion of image volume but requires considerable additional time and attention to execute properly. PET-CT has been playing an increasingly important role in the radiation therapy process, especially in multidisciplinary oncology centers [36, 38]. One of the essential advantages that PET-CT offers over CT alone is the detection of smaller lymph nodes that would not likely be considered positive on CT by size criteria . Additionally, there is now ample evidence that PET-CT consistently locates unsuspected distant metastatic disease that is not visible on CT alone . There are several possible approaches to incorporating radiation therapy planning into the PET-CT environment but 2 primary methods have emerged in more routine PET-CT clinical practice. The simplest method is to complete the PET-CT on a flat RT therapy planning pallet with the patient positioned in a manner approximating the positioning established or anticipated in the patient’s RT planning [36-39]. Figure 13 depicts a PET-CT scanner equipped with the RT pallet.
This approach requires no additional preparation other than the PET-CT staff receiving notification in advance to place the patient on the RT pallet. A more complex method is to position the patient in the same RT apparatus as created for the patient’s original simulation. In this case, the patient is instructed to bring their simulation position device with them to their PET-CT appointment.
The primary limiting factor for this approach is usually the bore of the PET-CT gantry [36, 40]. Most manufacturers now offer RT-sized PET-CT gantries because of the emerging complementary nature of RT and PET-CT . This approach permits the most accurate but also most complex and time-intensive approach with the simulation and PET-CT occurring all in one session. In this environment, the dosimetrist or radiation therapist will position the patient in their custom radiation therapy body cradle, thermoplastic mask, or similar radiation therapy simulation apparatus [36-38]. Figure 13 a and b depict a patient who has been fitted with the same thermoplastic mask as used in the patient’s actual radiation therapy. Figure 14 shows the fiducials together with RT planning “B pillar” viewed on the reconstructed images. The PET-CT image sets are then migrated to the radiation therapy planning software and used by the radiation oncologist and dosmetrist for the patient’s radiation therapy sessions. The advantage of this approach is that the PET-CT images acquired are the
9.3. Inpatients in the PET-CT environment
A final but important consideration for PET-CT acquisition is the additional maneuvers required for inpatient scanning. Inpatients will almost always require more time to ambulate, transition, and position in the PET-CT scanner. A corresponding increase in staff time must be planned for given the higher level of acuity inherent to inpatient scanning. A variety of imaging workflows and paradigms exist for incorporating inpatients into a busy imaging practice. One approach is to have an inpatient-only scanner dedicated exclusively to performing inpatient requests. This approach is more readily integrated in a large academic institution that has the resources for multiple scanners allocated for specific purposes. It is not well-suited to the typical, smaller imaging environment that relies on higher volume and more closely sequenced outpatients. Nevertheless, as the result of diminishing funds and resources, it has become increasingly common to perform inpatient studies in the outpatient setting. In any case, many institutions have found that a radiology RN is vital link in the preparation necessary to create a high-quality PET-CT scan. The RN should be available to perform a true peer-to-peer interaction with the patient’s RN prior to the patient’s actual arrival. This helps to insure the patient can be transported and maintained in the PET-CT department safely. Primary considerations include but are not limited to the following:
10. PET-CT image data distribution
Once the PET-CT image data has been acquired and processed, a convenient, rapid, and reliable system must exist to archive the image data. The historical arc of image archiving has spanned from hard-copy radiographic film systems to present day systems that permit viewing digital soft-copies of PET-CT images in Picture Archiving and Communication Systems (PACS). In most radiology and medical imaging settings, PACS has emerged as the preferred archival strategy although there continues to be a diversity of images rendered in the varied hospital and imaging center environments across the United States and globally.
PACS has been configured to support the extensive tomographic image production which is the result of torso axial coverage in the typical PET-CT. This has been especially important as multi-detector CT associated with PET has advanced and resulted in thinner and increased number of slices. It is not unusual for the combined PET-CT image set to contain in excess of 2000 image slices that require rapid transfer to the PACS server and corresponding distribution to image review workstations. Image transfer rates and efficiency will be a function of the bandwidth available throughout the hospital or imaging system network. Rate of image transfer is central to availability of image data on centralized and remote workstations. System slow-downs will also impact the performance of the PET-CT acquisitions if the processed data cannot be rapidly transferred to the PACS. This phenomenon is both vendor and system topology dependant but best practices require that an entire study be transmitted in under 5 minutes for a busy PET-CT imaging center. Figure 16 graphically depicts the relationship between image data transfer rate and transfer time. There is a clear exponential relationship which is quickly realized within the imaging workflow because transfer rate and time delays can cause backlogs and impair overall PET-CT system performance.
Given the opportunity, PET-CT, medical informatics professions, and information technology professionals should begin to collaborate early in the process of configuring PET-CT operations. This working relationship has become an imperative as image acquisition and corresponding PET-CT report turn-around-time have become an important metric in quantifying standard-of-care. The shape and layout of the network and nodes (topology) should be considered both before and during the establishing of the PET-CT infrastructure. For large hospital systems with multiple sites and remote viewing requirements, having a scalable network with very high bandwidth and redundancies will be paramount. This becomes a complicated and expensive undertaking as network cabling, switches, servers, and all manner of information technology infrastructure will need to be considered, purchased, deployed, and maintained over the course of many years. Figure17 illustrates an example of the configuration of a typical PET-CT system topology and interconnectivity. A clear understanding of the connectivity, dependence, and relationship of both hardware and software items is vital to initial troubleshooting during system failure. Many issues such as physical disconnection between devices due to lose cabling or locating of devices requiring a reboot can be identified simply by knowing the system topology and understanding the interrelationship of system components.
11. PET-CT image archiving and retrieval
11.1. PACS workflows
A consistent, reproducible, and accessible PACS workflow should be conceived and followed by the PET-CT staff who generate the images. In particular, it will be important to consider ancillary information that the radiologist requires to read the images and the accessibility of said materials [1, 38]. The PET-CT images are certainly the centerpiece of the exam but additional information such as pathology reports, consults, and imaging reports augment the interpretation process. There are three approaches to incorporating this information into the PACS workflow effectively. The first option will be to simply printout and provide the radiologist with any ancillary clinical information that will be used to render the report. This is the least desirable method because it involves a substantial shuffling of paper and usage of printer resources. However, many institutions still use the standard paper method because of the imaging culture of the institution. The 2nd option will be to forego any printing of documents and deliver these to the radiologist in a purely “paperless” or soft format. This will require a favorable and convenient adjacency of the Health Information System/Radiology Information System (HIS/RIS) to the PACS workstation. It also requires support staff to scan in any documents that are not native to the hospital or imaging center. The third option that occurs in highly integrated healthcare environments is a merger of PACS, HIS, & RIS all within the PACS environment. This requires maximum collaboration and cooperation of Radiology and Medical Informatics as well as appropriately planned monitor and screen real estate. In a well-planned and executed fully integrated PACS/HIS/RIS, the radiologist can readily navigate and among the aforementioned applications with minimal paper waste and stream lined workflow. Figure 18 shows a fully functional PACS/HIS/RIS configuration.
11.2. Non-PACS image distribution methodologies
In addition to PACS-based image viewing systems, it is inevitably necessary to view PET-CT images in other venues where PACS may not be available. Given that all data is DICOM-based, the best solution is to obtain the images on a solid-state media such as compact disk (CD) or digital video disk (DVD) and upload the data to PACS for viewing. This option also has the advantage of being executed on the user’s computer regardless of bandwidth limitations.
Hospital or imaging centers with virtual private networking (VPN) capability may use file transfer protocol (FTP) as a means of securely and reliably transferring image data. With contemporary firewall systems, this often becomes a challenging undertaking fraught with information technology issues that will require an advanced user with administrative system access capabilities. Invariably, however, many institutions lack a full PACS or means of securely transmitting image data via ftp. This includes many surgical suites outside of the hospital or imaging center where the PET-CT originated, as well as community-based oncology groups, and virtually any location beyond the reach of native PACS. For such situations, the next best option for viewing images will be client-server based viewing capabilities. This will involve providing the remote user with a username and password to authenticate with the PACS server and then streaming data to the remote user’s monitor. The distinct disadvantage of this method is that almost no PC-based client server monitors possess the appropriate resolution inherent to a PACS monitor that has true DICOM gray scale standard rendering [50, 51].
12. Internal archival methods
There are instances in which PACS does not provide a desirable location for storage. This is particularly true in instances whereby raw data sets such as PET or CT sinograms must be stored. This situation will commonly occur and be an imperative for research protocols that require the original raw data to be available in perpetuity. Sending the PET and/or CT sinograms across the network from the modality to PACS invariably results in raw data corruption resulting either in transmission failure or unusable data. Offline storage devices such as Redundant Arrays of Independent Disks (RAID) or terabyte hard drives are viable solutions in these cases. The compatibility of these options must first be vetted with the PET-CT scanner vendor to ensure long-term stability and recoverability of the raw data. These systems do have the advantage of being scalable as additional disk space can be added both to RAID and other types of offline hard drive systems [1, 38, 40].
From PET’s primary research-oriented imaging in the 1970s and 1980s to contemporary PET-CT routinely used for oncology and neurology, PET continues to play an important role in the management of and characterization of a wide variety of disease processes. PET-CT as practiced today remains one of the most challenging and complex type of imaging studies performed in most hospital or imaging center environment. This derives largely from the integration of 2 somewhat divergent modalities along with the multifaceted diagnostic requirements of patients in oncology and neurology. An understanding of the acquisition, processing, and archiving of PET-CT data is central to sustaining a safe, patient-centered and high-quality PET-CT image product.
The author wishes to thank Dr. Paul Shreve and the staff of the Spectrum Health Lemmen Holton PET-CT Cancer Pavilion for their insight and support in writing this chapter.