Background The use of fluoroscopic screening involves exposure to ionising radiation for both patients and operators.
Objective To assess the effects of radiation dose reduction manoeuvres (DRM) during radiofrequency ablation (RFA) procedures.
Design Prospective study of DRM.
Setting Tertiary cardiac centre.
Interventions Two DRM were combined: removal of the secondary radiation grid and programming an ultra-low pulsed fluoroscopy rate. These methods were assessed using an anthropomorphic phantom model to measure skin entrance dose rates. Procedures were classified as complex (ablation of atrial fibrillation, ventricular tachycardia or complex congenital heart disease arrhythmias) or simple (all other RFA).
Main outcome measures Dose area product and screening times were compared for ablations performed before and after DRM. Equivalent doses to organs and malignancy risk were determined by computer modelling.
Results Over a 39-month period, 1007 ablation procedures were performed (631 simple, 376 complex). Radiation dose was significantly reduced after DRM for both simple (20.4±26.9 Gycm2 vs 8.0±10.3 Gycm2, p<0.00001) and complex ablations (63.3±50.1 Gycm2 vs 32.8±31.7 Gycm2, p<0.00001) with no difference in screening times. The mean lifetime risk of fatal cancer attributable to radiation exposure per million procedures was reduced from 182 to 68 for simple ablations and from 440 to 155 for complex ablations.
Conclusions Significant reductions in radiation exposure during RFA were achieved using simple DRM, corresponding to a two-thirds reduction of the risk of excess fatal malignancy.
- Catheter ablation
- x-ray dose reduction
- fatal malignancy
- atrial arrhythmias
- radiofrequency ablation (RFA)
- atrial fibrillation
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- Catheter ablation
- x-ray dose reduction
- fatal malignancy
- atrial arrhythmias
- radiofrequency ablation (RFA)
- atrial fibrillation
The high success rate and low complication risks of radiofrequency ablation (RFA) have led to its increasing use as first line treatment for a number of cardiac arrhythmias.1 In recent years, with greater understanding of arrhythmia substrate and development of advanced electroanatomical mapping systems, RFA has emerged as a potential treatment option for more complex arrhythmias including atrial fibrillation (AF)2 and ventricular tachycardia.3 These factors have contributed to a rapid growth in the numbers of RFA performed worldwide. The majority of RFA procedures use fluoroscopic screening to guide catheter placement and therefore carry risks associated with exposure to ionising radiation including skin injury,4 5 radiation-induced malignancy6–8 and genetic effects.7–9 These are of particular concern for young patients and for patients undergoing long complex procedures, where high radiation doses have been reported6 and in whom repeated procedures may be indicated.10 Operators, particularly those performing high volumes of procedures, are also exposed to risks from radiation including malignancy.11 Many cardiac catheter laboratories use a secondary radiation grid to improve image resolution by reducing scatter at the image intensifier. Previous authors have shown that the presence of this grid typically doubles the radiation dose.12 Since high-definition imaging is not essential for most RFA cases, given the high radio-opacity of typical ablation catheters, we hypothesised that removal of the secondary radiation grids could reduce radiation exposure without affecting screening time. In addition, reduction of the fluoroscopy pulse rate could further reduce radiation dose for RFA.
The aims of this study were to assess the radiation reduction resulting from these dose reduction manoeuvres (DRM) using an anthropomorphic phantom model, and to measure total radiation dose for all types of RFA procedures performed routinely in an electrophysiology laboratory before and after DRM.
Radiation doses were assessed in the electrophysiology laboratory before and after DRM. x-Ray imaging was performed using a Philips Integris BH5000 biplane C-arm fluoroscopic unit (Philips Medical Systems, Eindhoven, the Netherlands), equipped with last image hold. The primary tube was positioned under the couch with the image intensifier above and was used for postero-anterior (PA) and right anterior oblique imaging. The lateral tube was used for left anterior oblique projections. Beam filtration consisted of 3.4 mm Al to which 0.2 mm Cu was added. During fluoroscopy, kilovoltage (40–110 kVp) and tube current (25 mA max) were selected by automatic brightness control. The focus to image intensifier distance was 100 cm. The Philips unit has real-time monitoring of fluoroscopy time and dose area product (DAP) measurement. DAP, the product of total radiation dose and the radiation field area, provides a measure of radiation exposure. DAP metre readings were calibrated using a Keithley 96035 parallel-plate diagnostic ion chamber and a Keithley 35050A Dosimeter (Keithley Instruments, USA) to measure radiation dose in the centre of the field while imaging an M1 Leeds test object with a wire matrix (Leeds Test Objects, UK) to measure the area of the field. DAP calibration measurements were done at 105 kVp, 12 mA for the AP tube and at 86 kVp, 21 mA for the lateral tube. The Keithley dosimeter and ion chamber were calibrated (with relative uncertainty 2.8% of the calibration factor) at the John Perry Radiation Metrology Laboratory (London, UK) using a secondary standard system with a current calibration from the Physikalisch-Technische Bundesanstalt (holder of the German national standard for x-ray dosimetry).
Radiation reduction methods
At baseline (pre-dose reduction), screening fluoroscopy was routinely performed at the factory ‘low’ setting of 12.5 pulses per second (pps) with a pulse length of 6 ms, and with the secondary radiation grid in situ. In order to reduce radiation dose, we programmed a customised ‘ultra-low’ fluoroscopy setting at 6.25 pps and removed the grid.
Direct measurement of skin entrance dose rate
An adult torso anthropomorphic phantom consisting of a natural human skeleton embedded in tissue equivalent rubber (Temex) was used to assess entrance skin dose rate using the Keithley dosimeter and ion chamber, positioned directly underneath the phantom. The position of the ionisation chamber in relation to the x-ray field was verified using fluoroscopy. Dose rates were obtained with the frontal tube in PA, right anterior oblique 30 degrees and, for the lateral tube, left anterior oblique 45 degrees, in keeping with the use of the two tubes in clinical practice. Dose rates were measured under automatic brightness control of kVp and mA for the 23 cm field of view during continuous irradiation for at least 30 s. The measurements were repeated for low and ultra-low fluoroscopy settings both with and without the secondary radiation grid.
Radiation doses in clinical cases
Following the phantom measurements, DRM were adopted in the electrophysiology laboratory for all RFA procedures. DAP and screening times were examined for the 17 months before and 22 months after DRM. Procedures were classified as ‘simple’ (ablation of accessory pathway, atrioventricular nodal re-entry tachycardia, typical caval-isthmus dependent atrial flutter, atrioventricular nodal ablation) or ‘complex’ (ablation of AF, atypical atrial flutter/tachycardias, ventricular tachycardia, or in patients with complex congenital heart disease). Diagnostic electrophysiological procedures were excluded. Conventional multipolar contact catheters were used for mapping and ablation, and all procedures were performed by experienced clinical operators. Non-fluoroscopic three-dimensional mapping systems (CARTO, Biosense Webster, California, USA or Ensite NavX, St Jude Medical, St Paul, Minnesota, USA) were used in conjunction with conventional electrophysiology mapping systems for navigation and electro-anatomical mapping to guide complex ablations.
Calculation of equivalent doses and effective doses
Equivalent doses to organs for the periods before and after DRM were calculated using the Monte Carlo based PCXMC simulation program (version 1.5), based on skin entrance dose rates and kVp values determined from the phantom measurements and the mean screening times and proportion of screening spent in each projection measured during the study periods. The PCXMC program was developed by the Radiation and Nuclear Safety Authority (STUK, Finland) for calculating patients' organ doses in radiography and fluoroscopy.13 A large number of individual photon histories are generated to reduce the statistical errors of organ doses, and estimates of the mean values of the energy depositions in the various organs of the phantom are used for calculating equivalent doses for these organs.14 Calculations were performed with a focus to skin distance of 80 cm and the x-ray beam collimated to the heart borders, using a simulation exposure of 10 million photons for each radiographic projection.
The lifetime fatal cancer probability for each organ was calculated as the product of the equivalent dose to the organ and the organ-specific fatal cancer probability coefficient, obtained from the 2007 recommendations of the International Commission on Radiological Protection (ICRP) approved in March 2007.15 The effective dose for each radiographic projection was calculated as the sum of the equivalent organ doses determined by the computer model, multiplied by the appropriate tissue weighting factors,15 and body effective dose was computed as the sum of effective doses for the three radiographic projections. The excess lifetime risk of malignancy (attributable to the RFA radiation) was then determined using the population-averaged probability coefficient 5.5% per Sv.15 The risk of radiation-induced hereditary effects was computed using doses to the ovaries (doses to the testes were negligible) multiplied by the risk coefficient for hereditary effects 0.2% per Sv.
Continuous data are presented as mean±SD. Ranges are given where appropriate. Unpaired Student's t tests were used to compare baseline characteristics and data before and after radiation reduction. A value of p<0.05 was considered significant.
Table 1 shows measurements of skin entrance dose rates obtained using the phantom. Reductions in dose rate were seen both with removal of the grid and reduction in fluoroscopy pulse rate. When ultra-low settings were combined with removal of the grid, dose rates were 60–65% lower than baseline measurements in all projections.
Operators were not informed of the changes made to the radiation during cases unless they commented on the quality of imaging. This occurred in only 9 cases and in no cases was there a request to increase the fluoroscopy frame rate; in only 5 post-DRM cases (2 simple, 3 complex) was there a request by the operator to replace the grid. Figure 1 shows examples of images of ablation catheters taken with and without the grid.
Between January 2004 and March 2007, 1007 ablation procedures were performed (631 simple, 376 complex). There were no differences in baseline characteristics between the two study periods for both simple and complex procedures (table 2). Standard equipment and catheters were used for simple ablation cases. All complex cases used a three-dimensional mapping system (Carto or NavX) to assist in navigation, mapping and ablation. There were no differences in procedure times for either simple or complex procedures pre- and post-DRM (table 2).
There were significant reductions in radiation DAP after dose reduction for both simple (20.4±26.9 Gycm2 vs 8.0±10.3 Gycm2, p<0.00001) and complex ablations (63.3±50.1 Gycm2 vs 32.8±31.7 Gycm2, p<0.00001). There was no difference in screening times: 20.3±16.6 min vs 21.3±18.5 min (p=0.55) for simple ablations and 55.3±28.1 min vs 52.7±23.3 min (p=0.43) for complex ablations (figure 2). There was no change in either the success rate or major complication rate for RFA procedures after dose reduction.
Equivalent doses for organs and malignancy risk
The computed equivalent organ doses for simple and complex ablations are shown in tables AI and AII in the appendix. The organ-specific probability coefficients (ICRP 2007)15 are also given along with the calculated fatal malignancy risk for each organ. Estimates of the lifetime risk of excess malignancy derived from the effective dose calculations are shown in table 3.
The risk of fatal malignancy related to x-ray exposure was reduced by 63% to 68 cases per million procedures for simple RFA and by 65% to 155 cases per million procedures for complex RFA. Malignancy risk is also given, corrected per hour of screening for comparison with published studies. The estimated risk of hereditary abnormalities post DRM is 6.4 per billion procedures for simple RFA and 14.2 per billion procedures for complex RFA.
The underlying principle of radiological protection, with respect to all medical radiation exposure, is that the radiation dose should be kept as low as reasonably achievable (ALARA). Although image quality provided by fluoroscopic systems has steadily improved over time, the highest resolution and best available image quality may not be required for all types of procedure. This study demonstrates that the use of ultra-low fluoroscopy and removal of the secondary radiation grid can significantly reduce radiation dose in the electrophysiology laboratory without increasing screening times. The effects of these measures on skin entrance dose rate were assessed using a standard phantom model before dose reduction in clinical cases was confirmed by studying a large number of procedures over a period of more than 3 years and comparing DAP measurements. DAP has been shown to have good agreement with other direct measurements of effective radiation dose in diagnostic radiology,16 cardiac fluoroscopy17 and RFA.7 18 Previously reported DAP values for simple RFA range from 11.6 to 251 Gycm2 compared to 8.1 Gycm2 in this study.18–20 Using the phantom data in a computer simulation model to calculate organ dose, we demonstrated an approximate two-thirds reduction in the risk of radiation-induced malignancy, for both simple and complex RFA.
Radiation reduction methods
Alterations to the fluoroscopy pulse rate or pulse width have been used to reduce radiation in cardiac pacing and in electrophysiology studies including ablations.20 This reduction in temporal resolution has no effect on image quality and in this study no operator requested that the pulse rate be increased after DRM. Radiation reduction by removal of the grid has been described in various settings including cardiac angiography.12 21 22 Scatter can be reduced without use of a grid by increasing the air gap to the image intensifier. However, the resultant increased magnification, particularly in laboratories with small detector plates as is typical in cardiac laboratories, does not allow visualisation of the entire heart. Physical removal of the grid, which is usually situated in a slot at the front of the image intensifier or attached to its surface, is in our experience a very simple process, taking a few seconds on commonly available systems (eg, manufactured by Philips, Siemens or GE). Similarly, if an operator requests replacement to improve image resolution, this can be achieved within seconds. However, this was only requested in a handful of cases in the present study. Important reductions in radiation dose have been achieved with the development of non-fluoroscopic imaging techniques, particularly in complex ablations,23 but this study shows that further reductions can be achieved using simple steps as mapping systems were used throughout this study period.
Comparison of radiation dose and malignancy risk with previous studies
Published studies show large variations in radiation dose during RFA; many of them describe small numbers of patients where ablation was performed in the setting of a specific radiation study rather than ‘real world’ cases such as in the present study. A variety of methods have been used to quantify radiation exposure during RFA6–8 24 25 and a number of approaches have been adopted to calculate malignancy risks in RFA.6–8 19 Table 4 summarises previously reported RFA studies along with the current study. Even when corrected for screening time, the malignancy risks associated with RFA in this study are up to 15 times lower than in other studies, and represent the lowest of all available published data.
Two studies have specifically investigated radiation doses in AF ablation [table 4]. Lickfett et al recorded doses from 15 procedures, using 50–60 thermoluminescent dosimeters attached to the patients.6 Even when the longer screening times in that study (129.7±36.7 min compared to 54.3±23.5 min in the present study) are taken into account, the mean effective doses are considerably higher than in the present study. Macle et al used a single electronic dosimeter, which provides an estimate of whole body effective dose based on a measurement at a single point, to record the personal dose equivalent to 43 patients.26 The low effective doses reported may have been underestimated due to the dosimeter, which was positioned over the xiphisternum, not being consistently in the primary beam as its position was not confirmed using screening and AP projection was not exclusively used.
Skin doses and deterministic effect thresholds
The reference threshold dose to skin for early transient erythema is 2 Gy and the FDA recommends that patient dose be monitored for any procedure which has the potential to exceed 1 Gy.27 Previous publications have suggested that this is not uncommon in RFA. In a study of skin doses in 500 RFAs, 5.6% of patients received enough radiation to reach the 2 Gy threshold dose.5 Of the 15 patients undergoing AF ablation in the Lickfett study, all but two patients exceeded the 1 Gy FDA threshold.6 In the present study the very low skin entrance dose rates (1.77 mGy per minute for the PA projection for the average person) mean that for most patients, reaching these thresholds is extremely unlikely.
Previous case reports and series have described prolonged screening times and high radiation doses in complex ablation in particular. We have shown that by using simple measures, radiation levels can be kept to levels where the risks of both deterministic and stochastic effects are very small. We report effective doses of 1.24 mSv and 2.83 mSv for simple and complex RFA, respectively. This compares to the average annual background radiation dose in the UK of 2.7 mSv28 and a typical dose of approximately 8 mSv associated with an abdominal CT. Another important clinical consideration is radiation exposure for operators and laboratory personnel, who may be involved in a large number of procedures. Although we did not measure operator exposure, reductions in patient dose have been shown to correlate with operator dose,25 29 and as the majority of operator exposure results from interaction of the x-ray beam with the patient, it is reasonable to expect that reductions in patient entrance dose translate to reduced operator dose. The described DRM could easily be adopted by many other centres, resulting in improved safety for patients and staff in the electrophysiology laboratory.
First, it should be noted that the use of ‘effective dose’ and its relationship with risk from radiation exposure was developed in population studies (ICRP) and is not recommended for estimating risks in individual patients. Second, although removal and replacement of the grid is extremely simple in the fluoroscopy equipment described in this paper and in other systems with which the authors are familiar, the process differs among systems and may be much more difficult in other laboratories. A further point when considering adopting these DRM in other laboratories is that programming an ‘ultra-low’ fluoroscopy setting may require the initial help of the medical physics department; however once it has been set up it is straight forward for the radiographer to select this setting for future cases. Finally, an important limitation of this study is that the calculations of effective dose are based on entrance doses measured in a phantom based on an average-sized person. Although this is in keeping with other published studies, it is important to recognise that heavier patients may be exposed to much higher doses.
Competing interests None.
Provenance and peer review Not commissioned; externally peer reviewed.
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