In large brain metastases (BM) with a diameter of more than 2 cm there is an increased risk of radionecrosis (RN) with standard stereotactic radiosurgery (SRS) dose prescription, while the normal tissue constraint is exceeded. The tumor control probability (TCP) with a single dose of 15 Gy is only 42%. This in silico study tests the hypothesis that isotoxic dose prescription (IDP) can increase the therapeutic ratio (TCP/Risk of RN) of SRS in large BM.
Materials and methods
A treatment-planning study with 8 perfectly spherical and 46 clinically realistic gross tumor volumes (GTV) was conducted. The effects of GTV size (0.5–4 cm diameter), set-up margins (0, 1, and 2 mm), and beam arrangements (coplanar vs non-coplanar) on the predicted TCP using IDP were assessed. For single-, three-, and five-fraction IDP dose–volume constraints of V12Gy = 10 cm3, V19.2Gy = 10 cm3, and a V20Gy = 20 cm3, respectively, were used to maintain a low risk of radionecrosis.
Results
In BM of 4 cm in diameter, the maximum achievable single-fraction IDP dose was 14 Gy compared to 15 Gy for standard SRS dose prescription, with respective TCPs of 32 and 42%. Fractionated SRS with IDP was needed to improve the TCP. For three- and five-fraction IDP, a maximum predicted TCP of 55 and 68% was achieved respectively (non-coplanar beams and a 1 mm GTV-PTV margin).
Conclusions
Using three-fraction or five-fraction IDP the predicted TCP can be increased safely to 55 and 68%, respectively, in large BM with a diameter of 4 cm with a low risk of RN. Using IDP, the therapeutic ratio of SRS in large BM can be increased compared to current SRS dose prescription.
Introduction
In stereotactic radiosurgery (SRS) for brain metastases (BM), the dose is generally prescribed according to a risk-adapted approach depending on the size of the planning target volume (PTV): for smaller PTVs higher SRS doses are prescribed than for larger PTVs with the aim to limit toxicity to acceptable levels in large BM [1]. In Radiation Therapy Oncology Group (RTOG) study 90-05, the maximum tolerated single-fraction dose for BM with a diameter >3 cm was 15 Gy, as a higher dose of 18 Gy was associated with an unacceptably high rate of severe central nervous system toxicity of 50% [3]. Recently, consensus was reached within the Netherlands for SRS dose prescriptions: a single dose of 24 Gy is prescribed to PTV sizes <1 cm3 and the dose level is stepwise decreased to 21, 18 and 15 Gy for PTV sizes between 1–10 cm3, between 10–20 cm3, and >20 cm3, respectively. In clinical practice, SRS is used for inoperable BM up to a diameter of 4 cm. The consequence of this PTV size-based dose prescription protocol is a 12-month local tumor control probability (TCP) of about 86% in small BM and a TCP of around 40% in large BM [4, 5]. Given the low TCP for large BM and taking into account that patients with large BM are often medically inoperable, there is a clear need for improvement of SRS in these patients, but not at the cost of an unacceptably high risk of toxicity. This is currently being investigated in phase I studies [6]. An alternative to PTV size-based dose prescription is isotoxic dose prescription (IDP) [7‐13]. The quintessence of this strategy is that the normal tissue tolerance level is always respected and used as a base for dose prescription. Thereby the risk of radionecrosis is kept low. The dose in the tumor is increased to the highest dose that is technically achievable and thereby maximizing the TCP while simultaneously respecting the normal tissue constraint. The IDP concept is different from the PTV size-based dose prescription approach, where fixed prescription doses are used that solely depend on the size of the target volume and for large BM do not respect the predefined dose–volume constraint for normal tissue. From previous studies of single-fraction SRS for BM, it is known that the risk of radionecrosis increases rapidly if the volume of the surrounding healthy brain tissue receiving at least 12 Gy is greater than 10 cm3 (that is, V12Gy > 10 cm3) [14‐16]. Apart from being dependent on the tumor prescription dose, the V12Gy also depends on the gross tumor volume-to-planning target-volume (GTV-PTV) margin used as well as on the beam arrangement (i. e., coplanar vs non-coplanar) that affect the degree of dose conformity and the steepness of the dose gradient at the outer rim of the PTV [17].
In this study, the hypothesis is tested that through IDP the predicted TCP in large BM up to 4 cm diameter can be improved from the disappointing low level of 42% that is obtained with a standard single SRS dose of 15 Gy while simultaneously respecting an acceptably low normal tissue complication probability (NTCP). Furthermore, the effects of GTV volume, different GTV-PTV margins, and beam arrangements on the predicted TCP are systematically assessed [4, 18, 19]. Both single-fraction and fractionated stereotactic radiotherapy (FSRS) IDP schemes are considered to assess the effect of fractionation.
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Materials and methods
This study comprises three phases. First, the potential to increase TCP under isotoxic conditions is investigated for single-fraction, three-fraction and five-fraction IDP schemes, with artificial BM having spherical GTV shapes of different diameters (0.5–4.0 cm, with stepwise increasing diameter of 0.5 cm, Table 1 for treatment plan characteristics). This allows us to systematically derive empirical relationships between the GTV size and the maximum achievable predicted TCP as a function of the GTV-PTV margin and the beam arrangement. Second, these results are compared against clinically delivered SRS treatment plans in 46 patients with realistically shaped GTVs.
Table 1
Characteristics of 48 SRS plans for artificially contoured BM
Nominal treatment plans: target-volume definition and treatment-planning technique
A computed tomography (CT) scan (Siemens Somatom Sensation Open, Erlangen, Germany) of an anonymized patient treated with SRS for BM was used to design nominal treatment plans having a dose prescription according to the Dutch consensus guidelines. The head and neck region was imaged until the claviculae with a slice thickness of 1 mm. In the treatment-planning system (Eclipse version 11.0.42, Varian, Palo Alto, CA, USA), 8 perfectly spherical GTVs with diameters ranging from 0.5 to 4.0 cm in steps of 0.5 cm were contoured in the right parietal lobe so that the brain stem and optic system did not overlap with the PTV. For each GTV, a PTV was created by isotropic expansion with a margin of 0, 1, and 2 mm. The dose prescription based on PTV size was a single fraction of 24, 21, 18, and 15 Gy for PTV sizes <1, 1–10, 10–20 cm3, and 20–65 cm3. With the prescribed dose, 99% of the PTV was covered, while having a steep dose gradient outside the PTV for brain sparing and allowing large dose inhomogeneity within the PTV. Per PTV, two 10 MV photon-based volumetric modulated arc therapy (VMAT, calculation grid size 1 × 1 × 1 mm3) plans were made by the same treatment planner, one with two overlapping coplanar arcs at a couch angle of 0° and one with three non-coplanar arcs having a couch angle of 0°, 45°, and 315° and a collimator angle of 30° or 330º. In total, 48 treatment plans were generated (Table 1). For each treatment plan, the V12Gy of the healthy brain minus the GTV was determined.
Renormalized treatment plans: IDP based on normal tissue dose constraint
For single-fraction IDP-based dose prescription, the nominal treatment plans with spherical GTVs were renormalized (by altering the monitor units) such that V12Gy = 10 cm3 for the healthy brain minus the GTV. The corresponding IDP dose levels for each of the 48 treatment plans were assessed for further analysis. The same procedure was used for the five-fraction IDP scheme, but a V20Gy = 20 cm3 constraint for the healthy brain minus the GTV was used instead [20]. For three-fraction IDP a V19.2Gy = 10 cm3 was used as a normal tissue constraint. This constraint was recalculated from the V12Gy = 10 cm3 using the linear quadratic model using an α/β ratio for brain tissue of 3. The predicted TCP was calculated from the IDP prescription dose by using a dose–response model that was statistically fitted to the data points of Wiggenraad et al. [4] (see Appendix). For calculation, plotting, and rescaling of the dose–volume histograms (DVHs), in-house developed MATLAB scripts (Version 8.5; The MathWorks, Inc., Natick, MA, USA) were used.
Validation of IDP results in clinically delivered SRS plans
Since in clinical practice the GTVs of BM are not perfectly spherical and the plan quality may slightly vary due to inter- and intratreatment planner differences, we compared the IDP dose levels obtained from the 48 treatment plans with perfectly spherical GTVs to those of clinical treatment plans comprising 46 consecutive patients who had been treated with SRS for a single BM at our institution between January 2013 and June 2014 with a dose of 15–24 Gy in 1–3 fractions. Patients had been considered eligible for SRS if they had a maximum of four BM from metastasized solid primary tumors (e. g., non-small cell lung cancer, breast cancer, colorectal cancer, melanoma, and bladder cancer) at the pretreatment contrast-enhanced magnetic resonance imaging (MRI) scan, a Karnofsky performance status of 70 or more, and extracranial treatment options. The selected cohort was identified from a database containing all patients who had been treated with SRS for newly diagnosed BM in our institution. Prior to treatment, a gadolinium contrast-enhanced MRI scan (3D T1-weighted sequence on a 1.5 T Ingenia/Intera or 3 T Achieva scanner, Philips Medical Systems, Eindhoven, Netherlands) was made with a slice thickness of 1 mm. Patients had been immobilized with a frameless mask and underwent an iodide contrast-enhanced CT scan (Siemens Somatom Sensation Open, Erlangen, Germany) with a slice thickness of 1 mm. For treatment-planning purposes, the MRI scan had been rigidly co-registered with the CT scan in Eclipse (Varian, Palo Alto, CA, USA). The BM had been delineated as GTV contours on the MRI scan and visually checked on the CT scan thereafter. A GTV-PTV margin of 2 mm had been applied. A VMAT (RapidArc) technique with 10 MV coplanar beams had been used to design the dose distribution for delivery with a TrueBeam STX linear accelerator (Varian, Palo Alto, CA, USA). To derive the IDP dose levels for our study, these treatment plans were renormalized such that the constraints V12Gy = 10 cm3, V19.2Gy = 10 cm3, and V20Gy = 20 cm3 were satisfied for the single-, three-, and five-fraction schemes, respectively.
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Statistical methods
The Pearson’s chi-squared test was used as a measure of fit between the IDP dose levels of the spherical GTVs and those of the non-spherical GTVs of the clinical plans. The difference between the coefficients of both exponential decay models was zero.
Results
The application of a non-zero GTV-PTV margin results in an increase in the PTV size and may hence influence the PTV size-based dose prescription and thereby the therapeutic ratio. As indicated by the change in symbol shapes in Fig. 1, applying a GTV-PTV margin of 1 mm instead of 0 mm resulted in lowering the nominal prescription dose from 21 to 18 Gy for a GTV diameter of 2.5 cm, while for the other 7 GTV diameters, the prescribed dose did not change. Applying a GTV-PTV margin of 2 mm instead of 0 mm resulted in decreasing the nominal prescription dose from 24 to 21 Gy, from 21 to 18 Gy, and from 18 to 15 Gy for GTV diameters of 1.0, 2.5, and 3.0 cm, respectively, while for the other 5 GTV diameters, the prescribed dose remained the same.
Fig. 1
Commonly used risk-adapted dose prescription based on PTV size and its effect on exceeding the normal tissue constraint for radionecrosis risk V12Gy = 10 cm3. The V12Gy as function of GTV size is presented for different GTV-PTV margins and beam arrangements. Legend: GTV gross tumor volume, PTV planning target volume, V12Gy volume of healthy brain tissue which is irradiated to 12 Gray or more. The GTV-PTV margin: 0 mm (a), 1 mm (b), and 2 mm (c). The open and filled symbols represent non-coplanar and coplanar beams, respectively. The single-fraction PTV size-based dose prescription: 24 Gy (triangle), 21 Gy (square), 18 Gy (diamond), and 15 Gy (circle)
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Applying a non-zero GTV-PTV margin also results in an increase of the dose absorbed in uninvolved healthy brain tissue and therefore affects the NTCP and therapeutic ratio. When the single-fraction PTV size-based dose prescription protocol is applied to the 8 perfectly spherical GTVs, V12Gy shows a clear tendency to increase with increasing GTV size and increasing GTV-PTV margin and is generally lower for the non-coplanar beam arrangement than for the coplanar beams (Fig. 1). From this figure, it is evident that for GTV diameters >2 cm, V12Gy exceeds the 10 cm3 constraint level irrespective of the GTV-PTV margin or the beam arrangement. Furthermore, this figure shows that for a GTV diameter of 4 cm, V12Gy is reduced from 33 cm3 to 13 cm3 in case a GTV-PTV margin of 0 mm instead of 2 mm is used in combination with non-coplanar beams instead of coplanar beams.
To test whether the single-fraction IDP dose levels derived for the spherical GTVs apply to the non-spherical GTVs of the clinical treatment plans, an empirical relationship between the PTV size of the spherical GTVs and the single-fraction IDP dose level was derived by fitting an exponential decay model to the data of the coplanar beam arrangement with a GTV-PTV margin of 2 mm (Fig. 2). The same was done for the IDP dose of the 46 clinical treatment plans with non-spherical PTVs. It could be shown that there is no statistically significant difference between these fits. The median (±SD) IDP dose difference between the spherical GTVs of the artificial treatment plans and the non-spherical GTVs of the clinical treatment plans was 0.25 ± 1.70 Gy and ranged from −3.92 to 2.16 Gy.
Fig. 2
Clinical validation of plan quality of the in silico SRS treatment plans with artificially contoured BM compared to clinically delivered SRS treatment plans in BM patients. A comparison of the single-fraction IDP dose level with V12Gy = 10 cm3 for coplanar beam arrangement and GTV-PTV margin of 2 mm between perfectly spherical GTVs (filled dots) and non-spherical GTVs of clinical plans (open dots). Legend: Gy Gray, GTV gross tumor volume, PTV planning target volume, SRS stereotactic radiosurgery, BM brain metastases, IDP isotoxic dose prescription, V12Gy volume of healthy brain tissue which is irradiated to 12 Gray or more. The solid lines represent single-fraction PTV size-based dose prescription protocols. The dashed line represents a logistic regression model fitted to data of perfectly spherical GTVs
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As shown in Fig. 3, for a 0 mm GTV-PTV margin, single-fraction IDP with the V12Gy = 10 cm3 constraint offers no potential for isotoxic dose escalation in spherical GTVs with diameters >2 cm, even when non-coplanar beams are used. For BM with a GTV diameter of 4 cm, this approach achieved an IDP dose of 14.1 Gy with a significantly lower TCP of 32% compared to the 42% that was predicted for the PTV size-based dose prescription at 15 Gy. Therefore, we have explored the potential of three-fraction and five-fraction IDP to increase the TCP, using a V19.2Gy = 10 cm3 and V20Gy = 20 cm3 respectively. For BM with a 4 cm diameter, using a 1 mm GTV-PTV margin and a non-coplanar beam arrangement, the predicted TCP was increased from 23% using single fraction IDP to 55 and 68% using a three-fraction IDP and five-fraction IDP respectively (Fig. 4).
Fig. 3
The prescribed dose and predicted TCP for single-fraction IDP with the V12Gy = 10 cm3 constraint as a function of the GTV diameter for coplanar and non-coplanar beam arrangements with a GTV-PTV margin of 0–2 mm and spherical GTVs. Legend: Gy Gray, GTV gross tumor volume, TCP tumor control probability, IDP isotoxic dose prescription, V12Gy volume of healthy brain tissue which is irradiated to 12 Gray or more, PTV planning target volume. A GTV-PTV margin enlargement results in an increase of the PTV size. An increase in the PTV size results in different cut-offs with a PTV size-based dose prescription with 24, 21, 18, and 15 Gy. The diamond (green line), circle (blue line), and cross (red line) represent the cut-offs with dose prescriptions with GTV-PTV margins of 0, 1, and 2 mm, respectively
Fig. 4
Potential of IDP to safely increase the TCP in large BM using a single, three-, and five-fraction schedule respectively. Legend: IDP isotoxic dose prescription, TCP tumor control probability, BM brain metastases, V12Gy volume of healty brain tissue which is irradiated to 12 Gray or more, V19.2Gy volume of healthy brain tissue which is irradiated to 19.2 Gray or more, V20Gy volume of healthy brain tissue which is irradiated to 20 Gray or more. The used normal tissue constraints were a V12Gy = 10 cm3, V19.2Gy = 10 cm3, and V20Gy = 20 cm3 for single, three-, and five- fraction IDP respectively
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Discussion
In this in silico study, the potential of IDP was investigated for improving the TCP from 42% with a single fraction of 15 Gy in large BM up to 4 cm diameter, while simultaneously respecting an acceptably low NTCP limit. The concept of IDP is of clinical relevance for BM with a diameter of 2 cm or more, as the constraint of a V12Gy of 10 cm3 for the surrounding brain tissue is exceeded with SRS independent of the GTV-PTV margin and the beam arrangement with the current PTV-based dose prescription (Fig. 1). In a large cohort of patients treated with SRS alone for a maximum of 3 BM, the median diameter of the BM was 2.3 cm, so this study is of relevance for at least half of BM patients treated with SRS in daily clinical practice [2]. Despite avoiding a GTV-PTV margin and exploiting a coplanar beam arrangement, the single-fraction IDP SRS approach with the V12Gy = 10 cm3 constraint for the nearby healthy brain tissue did not improve the predicted TCP over the standard SRS dose prescription with 15 Gy. As expected, five-fraction IDP had a better therapeutic ratio than single-fraction IDP. The predicted gain of from 32 to 73% in 1‑year TCP using five-fraction IDP instead of single-fraction IDP is significant. Such gain is especially relevant for oligometastases patients treated with curative intent in whom ablation of metastases and hence maximization of TCP is the goal. For patients with a relatively short life expectancy (for example, 6 months) treated with palliative intent, a lower 1‑year TCP could be considered acceptable. For these patients, a single-fraction approach having a relatively low 1‑year TCP may be preferred over a multiple-fraction approach for patient convenience.
To further improve the 1‑year TCP above 73%, the normal tissue constraint V20Gy = 20 cm3 needs to be relaxed, but this may result in an unacceptably high risk of radionecrosis. Alternatively, an approach with more than five fractions could be investigated if this approach increases the therapeutic ratio. The calculated TCPs are based on the model of Wiggenraad based on single-fraction SRS data for BM, and the same model was used to calculate the TCP with five fraction SRS [4]. However, a fractionated approach may be beneficial for re-oxygenation of the tumor, which may increase its radiosensitivity [21]. Therefore, the calculated TCP of 73% in very large BM (e. g., with a diameter of 4 cm) may be an underestimation of a clinically observed TCP using five fraction IDP. The current TCP model includes only prescription dose as a prognostic variable, but further extension of this model with other factors such as BM volume and possibly imaging characteristics reflecting hypoxia may further improve its accuracy. However, the influence of tumor size is difficult to quantify because in many series, lower doses are prescribed for larger BM or prescribed doses vary widely. Furthermore, the model needs to be externally validated and calibrated in other patient cohorts treated with SRS for BM. Dose–volume thresholds for an acceptably low risk of radionecrosis for schemes other than single-fraction and five-fraction SRS do not exist in literature.
To exploit the full potential of IDP in SRS, it is necessary to minimize the GTV-PTV margin and to optimize the beam arrangements by increasing the setup accuracy (6 degrees of freedom couch and a robust frameless mask) [22, 23]. Taking into account that the risk of radionecrosis increases rapidly above 10% as the V12Gy exceeds 10 cm3 for single-fraction SRS, it is clinically highly relevant to strive for a smaller GTV-PTV margin and to explore the feasibility of dose delivery with non-coplanar beam arrangements [14]. This is supported by a recently published randomized trial demonstrating that a decrease of the GTV-PTV margin from 3 to 1 mm does not decrease the local control probability for LINAC-based SRS [17]. As this study showed that there was a significantly larger V12Gy in the 3 mm GTV-PTV margin group, the authors stated that a 1 mm GTV-PTV margin should be used to avoid any unnecessary risk of radionecrosis and serious risk of neurologic morbidity.
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A limitation of our research is the lack of clinical validation of the models to predict TCP and NTCP. The TCP model is based on retrospective clinical studies [4]. Prospective clinical validation is needed for the NTCP model by using a V12Gy = 10 cm3 constraint for single-fraction IDP, a V19.2Gy = 10 cm3 constraint for three-fraction IDP, and a V20Gy = 20 cm3 constraint for five-fraction IDP [3, 14, 20].
In the last few years, much efforts have been made to safely increase the TCP of SRS in large BM using standard dose prescription and mild hypofractionation [24‐29]. However, in all these efforts the main drawback remains that a fixed dose will always result in a variety of radionecrosis risks with different sized BM. In a palliative setting of metastasized cancer patients it seems more appropriate to make the statement of “do not harm the patient”. Therefore the usage of IDP with the principle of a low risk of radionecrosis with any sized BM is preferable over fixed SRS dose prescription.
In conclusion, using three-fraction or five-fraction IDP the predicted TCP can be increased safely to 55 and 68% respectively in BM with a diameter of 4 cm with a low risk of radionecrosis. Using IDP, the therapeutic ratio of SRS in large BM can be increased compared to current SRS dose prescription.
Acknowledgements
The IDP concept was conceived, in part, from the development of an original protocol concept (Jaap D. Zindler) at the 16th Flims Workshop on Methods in Clinical Cancer Research held in June 2014 in Flims, Switzerland.
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Funding
The authors acknowledge financial support from the European Research Council (ERC) advanced grant (ERC-ADG-2015, n694812 Hypoximmuno) and the Dutch Technology Foundation STW (grant n10696 DuCAT and nP14-19 STRaTegy), which is the applied science division of NWO, and the Technology Program of the Ministry of Economic Affairs. The authors also acknowledge financial support from the European Union’s (EU) 7th Framework Program (ARTFORCE, n257144; REQUITE, n601826), SME Phase 2 (EU proposal 673780, RAIL), the European Program H2020-2015-17 (ImmunoSABR, n733008), Kankeronderzoekfonds Limburg from the Health Foundation Limburg, Alpe d’HuZes-KWF (DESIGN), and the Zuyderland-MAASTRO grant.
Conflict of interest
J.D. Zindler, J. Schiffelers, P. Lambin and A.L. Hoffmann declare that they have no competing interests. MAASTRO Clinic has a research agreement with Varian Medical Systems, Palo Alto, CA, USA.
Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made.
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In Wiggenraad et al. [4], a dose–response relation between the biologically effective dose of the linear-quadratic-cubic model using an α/β of 12 Gy (BED12) and the 12-month local control rates were constructed by eye fitting. Herein we obtained a statistical better fit by first digitizing the data points from Wiggenraad’s figure [4] using GraphClick software (version 3.0.2, Arizona Software) and subsequently fitting a logistic dose–response model by the maximum likelihood estimation:
where D = BED12, D50 is the BED12 at 50% local control, γ50 is the normalized slope at D50, and TCPmax is the asymptotic local control rate for large D. The fitted dose–response graph is shown in Fig. 5.
Fig. 5
A fitted dose-response curve based on data from Wiggenraad et al. [4]
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The model parameters obtained are D50 = 28.97 Gy (95% confidence interval [CI]: 24.80–33.14 Gy), γ50 = 1.41 (95% CI: 0.40–2.87), and TCPmax = 86.86% (95% CI: 70.62–103.10%).
