- Open Access
Passive proton therapy vs. IMRT planning study with focal boost for prostate cancer
Radiation Oncologyvolume 10, Article number: 213 (2015)
Exploiting biologic imaging, studies have been performed to boost dose to gross intraprostatic tumor volumes (GTV) while reducing dose elsewhere in the prostate. Interest in proton beams has increased due to superior normal-tissue sparing they afford. Our goal was to dosimetrically compare 3D conformal proton boost plans with intensity-modulated radiation therapy (IMRT) plans with respect to target coverage and avoiding organs at risk.
Treatment planning computer tomography scans of ten patients were selected. For each patient, two hypothetical but realistic GTVs each with a fixed volume were contoured in different anatomical locations of the prostate. IMRT and proton beam plans were created with a prescribed dose of 50.4 Gy to the initial planning target volume (PTV) including the PTV of the seminal vesicles (PSV), 70.2 Gy to the PTV of the prostate (PPS), and 90 Gy to the PTV of the gross tumor volumes (PGTVs). For proton plans, uncertainties of range and patient setup were accounted for; apertures were adjusted until the dose-volume coverage of PTVs matched that of the IMRT plan. For both plans, prescribed PTV doses were made identical to allow for comparing normal-tissue doses.
Protons delivered more homogeneous but less conformal doses to PGTVs than IMRT did and comparable doses to PSV and PPS. Volumes of bladder and rectum receiving doses higher than 65 Gy were similar for both plans. However, volumes receiving less than 65 Gy were significantly reduced, i.e., protons reduced integral dose by 45.6 % and 26.5 % for rectum and bladder, respectively. This volume-sparing was also seen in femoral heads and penile bulb.
Protons delivered comparable doses to targets in dose homogeneity and conformity and spared normal tissues from intermediate-to-low doses better than IMRT did. Further improvement of dose sparing and changes in homogeneity and conformity may be achieved by reducing proton range uncertainties and from implementing intensity modulation.
There has been a shift of radiation treatment paradigms towards organ-sparing focal treatments of the biologically significant lesions in advanced prostate cancer cases. This approach was envisioned by Ling et al.  who predicted that future radiation therapy would be based on conforming high doses to lesions of significant cancer, identified with biological imaging, while delivering lower doses to surrounding tissues.
This approach has been explored in planning studies of prostate cancer with intra-prostatic legions with intensity-modulated radiation therapy (IMRT) [2–6] as well as Phase I-II clinical studies [7–10]. The former has reported increased therapeutic ratios due to the local dose escalation and the latter reported comparable toxicity to treatments without local dose escalation [8–10]. The focal boost idea was extended to the use of proton beams by Schulte and Li .
External beam therapy with protons rather than photons is a topic of active discussion. At present, only a few comparative studies between IMRT and passively modulated proton therapy have been performed for prostate cancer. It was found that without compromising prostate coverage better sparing of normal tissues may be possible with proton beams [12, 13]. In this study, we comparatively evaluated boost treatment plans using passive proton beams and X-ray IMRT in ten prostate cancer cases by placing two hypothetical but realistic index GTVs into their prostate. The objective was to compare proton and IMRT plans with respect to target coverage and avoidance of normal tissues. To our knowledge, this is the first comparison of this kind.
Patient selection and volume definition
Ten computer tomography images, extending from L4 to 2 cm below the ischium, were selected from patients with intermediate- and high-risk prostate cancer treated by passive proton beams at Loma Linda University Medical Center. The study was approved by the Institutional Review Board at our institution. The prostate (PS) was delineated and seminal vesicles were contoured bilaterally and up to 1 cm proximally to the prostate. These regions formed the clinical target volumes (CTVs). Within PS, we chose two spherical index lesion GTVs with a volume of approximately 2 cc as shown in Fig. 1; one lesion was placed in the left lateral peripheral prostate zone, the most common location for macroscopic prostate cancer [2, 5], and centered in superior-inferior direction; the other was placed in the sagittal midplane adjacent to the bladder. The selection of the two GTVs was based on the following considerations: more than two lesions and/or a larger size would have excluded the use of a local boost; the size of 2 cc is representative of index lesions [2, 5]; the second GTV near the bladder, although not a common location, creates a dosimetric challenge to show a potential advantage of one technique over the other. The GTVs were delineated, giving them a spherical shape with each volume of 2 cc within +/− 10 %.
Bladder, bladder wall, rectum, and rectal wall were also delineated. The rectum and its wall were delineated from the level of the ischial tuborisities to the recto-sigmoid flexure. Right and left femoral heads, penile bulb, and external body were contoured as well. Patients were immobilized in a low-density foam shell placed inside a half-cylinder plastic pod. A setup-uncertainty/internal motion margin (SM) of 5 mm was added to the CTVs and GTVs according to our institutional policy, based on the use of rectal balloons . This resulted in the planning target volumes for the prostate (PPS), the seminal vesicles (PSV), and the GTVs (PGTVs). Both proton and IMRT plans were generated on the patients only excluding the pod in this planning study.
In our practice, we deliver 50.4 Gy to the PSV and 81 Gy to the PPS. In this study, we boosted the PGTVs to a dose of 90 Gy, while reducing the dose to the rest of PPS with microscopic disease to 70.2 Gy. We maintained 50.4 Gy to the PSV. Three sessions of 28, 11, and 11 fractions at 1.8 Gy/fraction can be delivered. As CTVs were expanded by the SM, some of the resulting PTVs overlapped with each other. Therefore, the PTVs effectively included PGTVs, PPS subtracted by PGTVs (PPS-PGTVs), and PSV-PPS.
Planning was performed with 7 equally spaced 6 MV beams starting from a gantry angle of 0° using a Varian iX accelerator (Varian Medical Systems, Inc., Palo Alto, CA) with a leaf width of 0.5 cm. The planning was done on the Odyssey planning system (Optivus Proton Therapy, Inc., CA) with a voxel size of 0.3 x 0.3 x 0.25 cm3. For inverse optimization, we imposed constraints of the Radiation Therapy Oncology Group (RTOG) Protocol 0815 as follows : all target volumes should receive their prescribed doses (PDs) to at least 98 % of their volumes; the minimum dose (D min ) within each target should be greater than 95 % of each PD; the maximum dose (D max ) within each target should not exceed 110 % of each PD (variation). Bladder constraints are as follows: no more than 15 % volume receives a dose that exceeds 80 Gy (V80 < 15 %); V75 < 25 %; V70 < 35 %; V65 < 50 %. The rectum constraints are: V75 < 15 %; V70 < 25 %; V65 < 35 %; V60 < 50 %. The mean penile bulb dose was constrained to < 52.5 Gy. In addition to the RTOG constraints, the maximum dose to femoral heads was limited to 50 Gy. The optimization was repeated until the constraints were met and no significant improvement in tumor coverage and organ savings was made by further optimization.
Two parallel-opposing lateral beams were applied to the combination of PPS and PSV to deliver a dose of 50.4 Gy, and a second set of two reduced beams was applied to the PPS to a total of 70.2 Gy. Finally, a left-lateral beam was applied to boost the dose to the two GTVs to a total of 90 Gy. Lateral beams have been traditionally used in proton therapy because they are most robust with respect to range uncertainties and mostly exclude bladder and rectum with their distal edges not pointed toward them [14, 16].
Appropriate distal and proximal margins were added to ensure coverage of the CTVs by the spread-out proton Bragg peak (SOBP) of each beam. For the margin determination, we employed a range uncertainty of 0.3 cm for uncertainties in accelerator energy, beam scattering foil thickness, and compensator bolus . We used an additional uncertainty of 3.5 % for CT accuracy (CT number conversion to proton stopping power), as shown in Eqs. (1) and (2).
Perpendicular to the beam direction, we adjusted the aperture margins until PTVs were dosimetrically covered, meeting the above target coverage requirements. This was done to compare the proton plans with the IMRT plans, which utilized the PTV concept. Of note, this approach was also adopted by the Children’s Oncology Group Protocol ACNS0831 when allowing proton therapy and IMRT .
To account for setup uncertainty that can affect proton range and to ensure full lateral scattering , the compensator (bolus) for each beam was “smeared” perpendicular to the beam direction by applying a smearing radius given by Eq. (3)
Plans were evaluated in terms of meeting the imposed planning constraints, integral dose (Gy cm3), and the inhomogeneity coefficient (IC), defined for each PTV as
where D max , D min , and D mean are the maximum, minimum, and mean PTV dose, respectively. The highest possible IC is zero. In addition, a conformity number (CN) as described in eq. (5) was used , which addresses both target coverage and normal tissue avoidance.
The highest possible CN is one. For comparative dose evaluation of IMRT and proton plans with respect to normal tissues, we applied the same dose prescription to both modalities. The dosimetric data and evaluation parameters were averaged over the ten cases and statistically evaluated by the Mann-Whitney test.
Results and discussion
Dose distributions of IMRT and proton plans are shown in Fig. 2. The dose distribution of the IMRT plan was contributed by conformal beam arrangement, while that for the proton plan by lateral arrangement.
Dose volume histograms of the two plans are provided in Fig. 3. The averaged planning data and plan evaluation parameters for the PTVs and normal tissues are given in Tables 1, 2, and 3. Table 1 shows that for both proton and IMRT plans, each PTV received a D min greater than 95 % of the PD. For brevity, the two PGTVs were evaluated together. For both plans, D max for the PGTVs was smaller than 110 % of the PD. However, the maximum dose constraints for PSV-PPS and PPS-PGTVs were exceeded due to their proximity to the PGTVs.
The average inhomogeneity indices of PPS-PGTVs and PGTVs was larger for IMRT plans (33.3 % and 9.7 %, respectively) compared to the proton plans (29 % and 4.6 %). This characteristic, i.e., the high-dose tail, is common to IMRT plans, whereas proton plans provide more homogeneous dose due to SOBP (Fig. 3a). However, for the PSV-PPS, the proton plan was more inhomogeneous than the IMRT plan (57.1 % vs. 49.1 %) due to spill over of higher doses from the PGTV coverage.
The average conformity indices were higher for the IMRT plans, although the difference was only significant for the PGTVs (35.8 % vs. 21.6 %). This can be explained by the fact that proton plans employed two lateral beam directions, whereas the IMRT plans were intensity-modulated with 7 directions.
The rectal volumes receiving doses >65 Gy were similar for IMRT and proton plans; the volumes receiving doses ≤65 Gy were reduced for protons, leading to an integral dose (ID) to the rectum reduced by 45.6 %, and to the rectal wall by 40.9 % (Table 2; Fig. 3b). The differences between protons and IMRT were somewhat similar for bladder; the volume receiving doses ≤45 Gy was smaller for proton beams (Table 2;Fig. 3b), leading to an ID to the bladder reduced by 26.5 %, and to the bladder wall by 17.9 %. Doses delivered to left femoral heads were significantly higher for the proton plans (Table 3;Fig. 3c), owing to the left lateral proton beam boosting the PGTV. The right lateral femoral head and penile bulb received similar doses for proton and IMRT plans. As seen in the table, all plans met the RTOG dose constraints. Concerning normal tissues outside the PTVs, proton plans delivered an ID that was 36.3 % less than that of IMRT plans.
Trofimov et al.  and Vargas et al.  compared IMRT and passive proton plans for prostate cancer. Different from our study, these investigators did not use a focal GTV boost; Trofimov et al., in addition to opposing lateral beams, adopted oblique beam angles and one IMPT plan; Vargas et al. optimized beam angles and reduced standard aperture margins by up to 30 % to spare bladder and rectum. Therefore, our findings of normal tissue coverage are not directly comparable to those by Trofimov and Vargas et al., although in agreement with them, substantially smaller dose was received by the volumes of rectum and bladder exposed to low-to-intermediate doses for proton plans.
Proton beams deliver more conformal and homogeneous dose, thanks to proximal and distal dose fall off and SOBP, than photons do. In this study, this disadvantage of photon beams was compensated by employing greater beam numbers and intensity modulation. Even without intensity modulation, passively scattered proton beams, using a lateral orientation, demonstrated dosimetric advantages in the low-to-intermediate dose range for critical organs and competing dose homogeneity and conformity for PTVs. Adoption of different orientations and/or increased beam number would further improve the proton plans (i.e. conformity), but we chose not to do so here, as GTVs are within CTV, another target, and the lateral beams are the most “robust” toward range uncertainties [14, 16].
Range uncertainties may decrease, and the conformity to PGTVs may change if we use scanning beams and improve imaging techniques [21, 22]. Additional range uncertainty due to uncertainty in RBE  may also be taken into account by implementing biologically-weighted treatment planning. Utilization of intensity modulation may also alter the conformity and the homogeneity to PGTVs and the homogeneity outside the PGTVs and inside PCTVs (PPS in this study), while the advantages in the low-do-intermediate dose and integral dose are retained. Lastly, as intensity modulation is implemented, there could be an interplay between interfraction organ motion and IMPT dose delivery that should be studied using repeated CT studies, deformable image registration, and dose summation .
For successful boost therapy, enhanced dose conformity to the PGTVs and homogeneity outside the PGTV would be better accepted by the treating physician. How much this will be translated into improved outcomes can only be demonstrated in future clinical trials. The boosting concept for intraprostatic dominant lesions is a rather new idea that has yet to be tested in (best randomized) clinical trials stratified by boosting technique. Initial single-institution experiences cited in the introduction of our paper, point toward feasibility and a favorable clinical outcome, but further clinical evidence needs to be accumulated and should also include novel modalities such as protons.
This paper intended to perform a dosimetric comparison with existing and widely practiced proton beam delivery techniques. In the future, one could also consider an integrated simultaneous boost technique rather than sequential delivery of the GTV boost. A simultaneous boost would be potentially more accurate because it would not require a different patient setup. The implementation of this technique can be made possible by IMPT.
This study reported reduction of volumes receiving low-to-intermediate dose and integral dose by proton beams. The use of protons for reducing clinical toxicity is a very active area of ongoing clinical study . and currently the most convincing data that a reduction of volume receiving low-to-intermediate dose afforded by proton therapy to less side effects came from the experience in head and neck cancer . Regarding the impact of lower integral doses, the clinical benefits are also demonstrated in gastrointestinal radiotherapy, e.g., [26, 27]. We believe that benefits will eventually be seen when more normal tissue is spared with proton radiotherapy of prostate cancer, but this needs further evidence from prospective clinical trials.
We have performed a first study that compares proton plans with IMRT for prostate cancers with intraprostatic lesions. Compared with IMRT, passive proton beams produced comparable doses to targets in dose homogeneity and conformity and spared normal tissues from intermediate-to-low doses better. Therefore, passive proton beams can be an advantageous choice for treating prostate cancers with a local boost. Further improvement of dose sparing and changes in homogeneity and conformity may be achieved by reducing proton range uncertainties and from implementing intensity modulation.
Gross intraprostatic tumor volumes
Intensity-modulated radiation therapy
Planning target volume
PTV of prostate
PTV of gross tumor volume
PTV of seminal vesicles
Clinical target volume
PPS subtracted by PGTV; PSV-PPS PSV subtracted by PPS
Radiation Therapy Oncology Group
- D max :
- D min :
- D mean :
Spread-out Bragg peak
Children’s Oncology Group
Ling CC, Humm J, Larson S, Amols H, Fuks Z, Leibel S, et al. Towards multidimensional radiotherapy (MD-CRT): Biological imaging and biological conformality. Int J Radiat Oncol Biol Phys. 2000;47:551–60.
van Lin ENJT, Futterer JJ, Heijmink SWTPJ, van der Vight LP, Hoffman AL, van Kollenburg P, et al. IMRT boost dose planning on dominant intraprostatic lesions: gold marker-based three-dimensional fusion of CT with dynamic contrast-enhanced and H1-spetroscopic MRI. Int J Radiat Oncol Biol Phys. 2006;65:291–303.
Pickett B, Vigneault E, Kurhanewicz J, Verhey L, Roach M. Static field intensity modulation to treat a dominant intra-prostatic lesion to 90 Gy compared to seven field 3-dimensional radiotherapy. Int J Radiat Oncol Biol Phys. 1999;43:921–9.
Xia P, Pickett B, Vigneault E, Verhey L, Roach M. Forward or inversely planned segmental multileaf collimator IMRT and sequential tomotherapy to treat multiple dominant intra-prostatic lesion of prostate cancer to 90 Gy. Int J Radiat Oncol Biol Phys. 2001;51:244–54.
Seppälä J, Seppänen M, Arponen E, Lindholm P, Minn H. Carbon-11 acetate PET/CT based dose escalated IMRT in prostate cancer. Radiother Oncol. 2009;93:234–40.
Pinkawa M, Attieh C, Piroth M, Holy R, Nussen S, Klotz J, et al. Dose-escalation using intensity-modulated radiotherapy for prostate cancer-Evaluation of the dose distribution with and without 18F-choline PET-CT detected simultaneous integrated boost. Radiat Oncol. 2009;93:213–9.
Dibiase S, Hosseinzadeh K, Gullapalli R, Jacobs SC, Naslund MJ, Sklar GN. Magnetic resonance spectroscopic imaging-guided brachytherapy for localized prostate cancer. Int J Radiation Oncol Biol Phys. 2002;52:429–38.
Pinkawa M, Piroth M, Holy R, Klotz J, Djukic V, Corral NE. Dose-escalation using intensity-modulated radiotherapy for prostate cancer-evaluation of quality of life with and without 18F-choline PET-CT detected simultaneous integrated boost. Radiat Oncol. 2012;7:1–9.
Fonteyne V, Villeirs G, Speleers B, de Neve W, de Wagter C, Lumen N, et al. Intensity-modulated radiotherapy as primary therapy for prostate cancer: report on acute toxicity after dose escalation with simultaneous integrated boost to intraprostatic lesion. Int J Radiat Oncol Biol Phys. 2008;72:799–807.
De Meerleer G, Villeirs G, Bral S, Paelinck L, de Gersem W, Dekuyper P. The magnetic resonance detected intraprostatic lesion in prostate cancer: planning and delivery of intensity-modulated radiotherapy. Radiother Oncol. 2005;75:325–33.
Schulte RW, Li T. Innovative strategies for image-guided proton treatment of prostate cancer. Technol Cancer Res Treat. 2006;5:91–100.
Vargas C, Fryer A, Mahajan C, Indelicato D, Horne D, Chellini A. Dose-volume comparison of proton therapy and intensity-modulated radiotherapy for prostate cancer. Int J Radiat Oncol Biol Phys. 2008;70:744–51.
Trofimov A, Nguyen PL, Coen JJ, Doppke KP, Schneider R J, Adams JA. Radiotherapy treatment of early-stage prostate cancer with IMRT and protons: A treatment planning comparison. Int J Radiat Oncol Biol Phys. 2007;69:444–53.
Slater J, Rossi Jr C, Yonemoto L, Bush D, Jabola BR, Levy RP, et al. Proton therapy for prostate cancer: the initial Loma Linda university experience. Int J Radiat Oncol Biol Phys. 2004;59:348–52.
Radiation Therapy Oncology Group. A phase III prospective randomized trial of dose-escalated radiotherapy with or without short-term androgen deprivation therapy for patients with intermediate-risk prostate cancer. Philadelphia PA; RTOG0815 2012:11–12.
Soukup M, Söhn M, Yan D, Liang J, Alber M. Study of robustness of IMPT and IMRT for prostate cancer against organ movement. Int J Radiat Oncol Biol Phys. 2009;75:941–9.
Moyers MF, Miller DW, Bush DA, Slater JD. Methodologies and tools for proton beam design for lung tumors. Int J Radiat Oncol Biol Phys. 2001;49:1429–38.
Children’s Oncology Group. Phase III Randomized trial of post-radiation chemotherapy in patients with newly diagnosed ependymoma ages 1 to 21 years. Monrovia CA; ACNS0831 2010:67–70.
Urie M, Goitein M, Holley MWR, Chen GTY. Degradation of the Bragg peak due to inhomogeneities. Phys Med Biol. 1986;31:1–15.
van't Riet A, Mak AC, Moerland MA, Elders LH, van der Zee W. A conformation number to quantify the degree of conformality in brachytherapy and external beam irradiation: application to the prostate. Int J Radiat Oncol Biol Phys. 1997;37:731–6.
Yang M, Virshup G, Clayton J, Zhu XR, Mohan R, Dong L. Theoretical variance analysis of single- and dual-energy computed tomography methods for calculating proton stopping power ratios of biological tissues. Phys Med Biol. 2010;55:1343–62.
Schulte RW, Bashkirov V, Klock MCL, Li T, Wroe AJ, Evseev I. Density resolution of proton computed tomography. Med Phys. 2005;32:1035–46.
Paganetti H. Range uncertainties in proton therapy and the role of Monte Carlo simulations. Phys Med Biol. 2012;57:R99–117.
Henderson RH, Hoppe BS, Marcus Jr RB, Mendenhall WM, Nichols RC, Li Z. Urinary functional outcomes and toxicity five years after proton therapy for low- and intermediate-risk prostate cancer: results of two prospective trials. Acta Oncol. 2013;52(3):463–9.
Chan AW, Liebsch NJ. Proton radiation therapy or head and neck cancer. J Surg Oncol. 2008;97(8):697–700.
Baglan KL, Frazier RC, Yan D, Huang RR. Martinez AA. The dose-volume relationship of acute small bowel toxicity from concurrent 5-FU-based chemotherapy and radiation therapy for rectal cancer. Int J Radiat Oncol Biol Phys. 2002;52:176–83.
Tho LM, Glegg M, Paterson J, Yap C, MacLeod A, McCabe M. Acute small bowel toxicity and preoperative chemoradiotherapy for rectal cancer: investigating dose-volume relationships and role for inverse planning. Int J Radiat Oncol Biol Phys. 2006;66:505–13.
Authors appreciate the statistical evaluation performed by Mr. Roger Grove.
The authors declare that they have no competing interests.
IY: As a principal researcher, he participated in treatment plan generation, study design, data interpretation, and manuscript writing. PN, IG, and SB: They participated in treatment plan generation and study design. RS: He participated in study design, proton planning description, data interpretation, and manuscript writing. AG and NW: They participated in proton treatment plan interpretation and planning algorithm description. GY, DB, TL, and JS: They participated in study design. They provided patient data base, physicians’ clinical input and critical review of the results of this study. BP: He participated in critical review of the results of this study and study design. All authors read and approved the final manuscript.