Development of a compact cavity BPM for real-time monitoring of clinical proton beams at HUST-PTF
Jiqing Li, Yuexin Lu, Jiapeng Li, Jian Wang, Zhengzheng Liu, Oleg Meshkov, Jinfeng Yang, Kuanjun Fan
TL;DR
This paper introduces a new compact beam position monitor for proton therapy that enables real-time monitoring of low-intensity proton beams with high precision.
Contribution
The novel off-center rectangular cavity BPM design with dielectric loading achieves high sensitivity for low-intensity clinical proton beams.
Findings
The BPM prototype achieved minimum sensitivities of 0.49 nV/mm at 70 MeV and 17.12 nV/mm at 230 MeV.
The device enables submillimeter stability (± 0.5 mm) for real-time beam orbit feedback correction.
The BPM can also verify beam energy through the phase of its signal.
Abstract
To ensure the safety and efficacy of precise proton therapy, real-time and non-intrusive monitoring of the clinical beam position is essential. However, in cyclotron-based proton therapy facilities, clinical proton beams with low repetition frequency and exceptionally low intensity due to the Energy Selection Systems (ESS), pose considerable challenges for accurate online beam diagnostics. Conventional non-interceptive beam diagnostic devices lack the sensitivity required to detect such weak beams with sufficient precision. This paper presents an innovative solution to this challenge: an off-centerrectangular cavity Beam Position Monitor (BPM) with dielectric loading. This novel design achieves remarkable position sensitivity while maintaining compact transverse dimensions of 500×250×100 mm. A prototype of this cavity has been fabricated and tested offline. Experimental results…
Genes, proteins, chemicals, diseases, species, mutations and cell lines named across the full text — each resolved to its canonical identifier and authoritative record.
Click any figure to enlarge with its caption.
Figure 1
Figure 2
Figure 3
Figure 4
Figure 5
Figure 6
Figure 7
Figure 8
Figure 9
Figure 10
Figure 11
Figure 12
Figure 13
Figure 14
Figure 15
Figure 16
Figure 17| Parameters | Value |
|---|---|
| Extraction beam energy | 250 MeV |
| Beam current from the cyclotron | >500 nA |
| Clinical beam energy | 70–230 MeV |
| Beam current after the ESS | 0.35–5 nA |
| Cyclotron RF frequency | 73 MHz |
| R/Q | Offset in | |||||
|---|---|---|---|---|---|---|
| 0 mm | 2 mm | 4 mm | 6 mm | 8 mm | 10 mm | |
| Theoretical (Ω) | 18.660 | 18.660 | 18.660 | 18.659 | 18.658 | 18.657 |
| CST Simulation (Ω) | 18.667 | 18.667 | 18.666 | 18.665 | 18.665 | 18.664 |
| Discrepancies | 0.04% | 0.04% | 0.03% | 0.03% | 0.04% | 0.04% |
| R/Q | Offset in | |||||
|---|---|---|---|---|---|---|
| 0 mm | 2 mm | 4 mm | 6 mm | 8 mm | 10 mm | |
| Theoretical (Ω) | 18.660 | 18.456 | 18.252 | 18.048 | 17.844 | 17.640 |
| CST Simulation (Ω) | 18.667 | 18.463 | 18.259 | 18.056 | 17.853 | 17.647 |
| Discrepancies | 0.04% | 0.04% | 0.04% | 0.04% | 0.05% | 0.04% |
| Beam energy (MeV) | Beam current (nA) | Position sensitivity (nV/mm) | Position accuracy (mm) |
|---|---|---|---|
| 70 | 0.35 | 0.49 | 0.65 |
| 110 | 1.38 | 3.12 | 0.10 |
| 150 | 1.81 | 5.13 | 0.06 |
| 210 | 3.41 | 11.46 | 0.03 |
| 230 | 5.00 | 17.12 | 0.02 |
Peer Reviews
No public reviews on file for this paper yet. If you reviewed it on a platform where reviews are public (OpenReview, ICLR, NeurIPS, ICML), you can paste yours below so the community can read it here.
Videos
No videos yet. Explain this paper in a talk, walkthrough, or lecture? Add one.
Taxonomy
TopicsRadiation Therapy and Dosimetry · Particle accelerators and beam dynamics · Radiation Effects in Electronics
Introduction
1
Proton therapy is becoming the preferred treatment globally because of its precision in targeting tumors (1–3). The Proton Therapy Facility (PTF) at Huazhong University of Science and Technology (HUST) is currently under commissioning (4–6). As depicted in Figure 1, this facility includes a 250 MeV superconducting cyclotron, a beam transport line, two rotating gantries, and a fixed treatment room. Table 1 lists the key parameters. A Graphite-based energy degrader is utilized to modify the cyclotron’s fixed energy to a variable range from 70–230 MeV (6). The ESS integrates collimators with a double bend achromat (DBA) dispersive-free section, discriminatively transmitting protons within target energy windows while suppressing high-scatter-angle particles at the expense of reduced transmission. This dual-stage filtering mechanism ensures beam parameters comply with rigorous clinical specifications (energy spread<1%, emittance<5 π mm·mrad). For instance, at an energy of 230 MeV, only 8.34% of the scattered beam is transmitted through the ESS; this transmission efficiency decreases to 0.07% when the beam energy is reduced to 70 MeV (6). Once they have passed through the ESS, the protons travel approximately 50 meters along a beam transport line before reaching the nozzle, where ion chambers are for beam monitoring.
Schematic layout of HUST-PTF.
However, in practical beam transport lines, various factors, such as errors in the dipole magnetic field and magnet positioning, can cause protons to deviate from their intended path, resulting in orbit distortions. These deviations can reduce the precision of proton beam dose delivery. Implementing real-time orbit correction can mitigate this and maintain the proton beam’s optimal trajectory. Precise control requires rapid, accurate, online measurements of the beam’s intensity and position throughout the transport line.
However, conventional beam diagnostic devices cannot detect proton beams of approximately 0.35 nA, necessitating the use of interceptive diagnostic devices (7), such as fluorescent screens and Faraday cups, for commissioning in a section-by-section manner. Although ionization chambers (8, 9) are highly sensitive for measuring beam current and position, their scattering interactions can degrade beam quality, especially when multiple ionization chambers are employed along the beam transfer line.
Clinical treatment could benefit from continuous monitoring of proton beams throughout their entire journey rather than merely measured at the beamline’s beginning or end. To achieve non-interceptive tracking, we can measure either the image current (10, 11) or the excited electromagnetic (EM) fields within an RF cavity (12, 13). Image current devices often lack the necessary sensitivity to monitor these beams.
In contrast, cavity-type beam diagnostic devices (14–16) (including Beam Current Monitors (BCMs) and cavity Beam Position Monitors (BPMs)) offer an advantage as cavity resonance improves the signal-to-noise ratio. Traditional cavity BPMs, often using a pillbox structure, are widely used in electron accelerators. Operating in the C-X band (3–9 GHz), their resonant cavities can be designed with compact dimensions. However, using conventional cavity BPMs for the HUST-PTF transport line poses significant challenges. First, the proton beam’s microstructure, tied to the cyclotron’s operating frequency (73 MHz), is too low for traditional cavity BPMs. Resonating at this frequency would require impractically large transverse dimensions. Second, conventional cavity BPMs operate in a dipole mode with low beam excitation efficiency. For the clinical proton beam currents around 0.35nA, the signal cannot be detected from the noise.
In order to overcome the above challenges faced in traditional models, recently, innovative designs in cavity BCMs and BPMs have been developed for the HUST-PTF. A novel prototype of a compact cavity BCM that demonstrated the feasibility of reducing cavity size through dielectric loading has been reported (17). This paper proposes the use of an off-center rectangular cavity BPM, also employing dielectric loading, which operates in the fundamental mode.
Cavity BPM pick-up principle
2
Working modes
2.1
An ideal cavity is an empty space enclosed by conducting walls that allow electromagnetic (EM) fields to be generated and confined when charged bunches pass longitudinally through it. A cavity designed to excite only transverse magnetic (TM) modes will have a vanishing longitudinal component of the magnetic field and an electric field aligned with the beam path. This alignment provides a strong coupling between the cavity and the beam. The electromagnetic field produced contains information on the beam, which can be measured.
This paper presents the use of a rectangular cavity for beam position measurement. A rectangular cavity is easier to fabricate compared to a cylinder. It provides sufficient beam position measurement accuracy and can measure horizontal or vertical positions separately. This cavity is designed with dimensions of 500×250×100 mm, and beam holes are incorporated into the walls to allow for coupling with the beams. In the case of a rectangular cavity, the monopole and dipole modes are used. Figure 2 shows the electromagnetic field modes. The monopole mode TM110 (Figure 2a) can be easily excited and has the strongest electric field in the center of the cavity. The excited electric field is directly proportional to the bunch charge and is concentrated almost exclusively around the center region, making it ideal for applications such as beam acceleration or intensity detection. In contrast, the dipole mode TM120 (Figure 2b) has a frequency that is close to that of the monopole mode. Its electromagnetic fields are mirror symmetric and increase linearly in the y direction near the center of the cavity. Since TM120 mode exhibits linear field growth along the y-axis with x-independence, this configuration inherently enables spatial decoupling of x-directional contributions from y-position monitoring. However, to simultaneously achieve x-directional beam position measurement, an orthogonally positioned identical structure is required to establish independent field monitoring channels.
EM field patterns of (a) monopole and (b) dipole modes in a rectangular cavity.
Working frequency
2.2
The eigenfrequency of TM modes only takes discrete values determined exclusively by the dimensions of the cavity. The resonant frequency of the TMmnp mode in a rectangular cavity is given by the following Equation:
In this Equation, m, n, and p represent the mode indices, while a, b, and L are the cavity dimensions along the x, y, and z axes, respectively. Here, c denotes the speed of light in a vacuum.
The resonant frequency of the TMmnp decreases as the transverse dimensions increase. In periodic multi-bunch diagnostics, cavities are typically tuned to an integer multiple of the bunch microstructure frequency. In the HUST - PTF, the microstructure frequency is 73 MHz, which is determined by the operating frequency of the superconducting cyclotron. To downsize the cavity-type BPM, its operating frequency is set at 146 MHz, precisely twice the repetition frequency of the proton microstructure.
Shunt impedance
2.3
To estimate the resolution expected from the cavity BPMs, further analysis of the energy exchange between the beam and the cavity is essential. This interaction is influenced by both the cavity’s geometry and the proton microstructure properties, which are characterized by shunt impedance (a critical parameter). Higher shunt impedance results in a higher sensitivity to the beam position. The normalized shunt impedance for each operational mode serves as a critical parameter for this assessment, which is defined as the shunt impedance divided by the unloaded quality factor (*R_sh_ */Q 0) (12, 15, 18), expressed mathematically as Equation 2:
Where V ext represents the excited voltage across the cavity, ω denotes the resonance frequency, and U is the storage energy within the cavity.
For example, if a rectangle cavity works in the TM110 mode, the normalized shunt impedance in the center region (y=0) is defined as Equation 3:
Here, a, b, and L denote the cavity dimensions along the x, y, and z axes, respectively; T represents the transient factor; and ϵ_0_ is the permittivity of free space. Increasing the normalized shunt impendence increases the beam position monitor signal.
Design and optimization of the BPM cavity
3
The signal-to-noise ratio (SNR) increases with the beam’s energy loss to the operational mode and external coupling efficiency. Conventional cavity BPMs with no dielectric are not suitable for monitoring the clinical proton of HUST-PTF due to two major challenges. Firstly, as clearly shown by Equation 1, the low operating frequency (146 MHz) results in a large transverse size. Secondly, conventional cavity BPMs utilizing dipole modes exhibit significantly weaker electric field intensity compared to the fundamental mode. This inherent limitation results in weak signal generation during low-intensity proton beam detection, consequently compromising SNR.
Off-center rectangular cavity works in monopole mode
3.1
To address these challenges mentioned above, the proposed solution is a novel rectangular cavity BPM with an off-center beam pipe working in monopole mode with dielectric loading, as shown in Figure 3. Cavity BPMs traditionally use secondary operation modes (dipole modes). At the same operating frequency, their transverse dimensions are larger than those of cavities operating with fundamental modes. Equation 1 shows that when the operating frequency is 146 MHz, the transverse dimensions of a rectangular resonant cavity (with an aspect ratio of 2:1) working in the TM120 mode are 4236 mm × 2118 mm, which is too large for practical applications. Furthermore, the longitudinal electric field excited in the dipole modes is weaker than that of fundamental modes. This results in a lower signal amplitude being extracted from the TM120 mode, which, in turn, limits sensitivity. In contrast, operating in the TM110 mode reduces the transverse dimensions of the cavity to 2298 mm × 1149 mm, a 71% reduction in the transverse area.
Rectangular cavity with off-center beam pipe.
GSI proposed using the fundamental mode TM110 in a rectangular cavity to measure the beam’s transverse position to improve the cavity BPM’s sensitivity and simultaneously reduce its transverse dimensions (19, 20). For a rectangular resonant cavity with dimensions a, b, and L along the transverse length, width, and longitudinal height, respectively, the longitudinal normalized shunt impedance expression for the TM110 mode is given by Equation 4:
In the region of the central axis of the rectangular cavity, the normalized shunt impedance for the TM110 mode remains essentially unchanged. However, if the center position of the beam pipe is shifted to the middle of the short semi-axis of the rectangular cavity (see Figure 3), then near the center of the beam pipe where x=x’ and y=1/4b+y’ (where x’ and y’ represent the displacement of the beam from the center of the beam pipe), substituting the expressions for x and y into the normalized shunt impedance equation yields Equation 5:
for y’<<b,
Equation 6 clearly shows that modifying the beam pipe’s position makes *R_sh_
- dependent on y’. This ensures accurate beam position measurements while maintaining the enhanced output signal characteristics of the TM110 mode.
According to Equation 6, when the center of the beam pipe is aligned with the midpoint of the short semi-axis of the rectangular cavity, the normalized shunt impedance exhibits minimal sensitivity to small displacements of the beam in the x-direction. In contrast, displacements in y primarily affect the normalized shunt impedance.
For a cavity length of 100 mm, we have theoretically calculated and simulated the normalized shunt impedance values for various transverse positions near the center of the beam pipe using CST Microwave Studio. The results are presented in Tables 2, 3, together with the results from Equation (6). Notably, the Normalized Shunt Impedance (NSI) values derived from Equation (6) agree within 0.04% with CST simulations, with discrepancies remaining within 0.1%. Figure 4a shows the calculation results.
*Normalized shunt impedance within the beam pipe. (a) CST Simulated data of Tables 1 , 2
(b) 2D map of normalized shunt impedance from the CST simulation.*
The CST simulation shows that *R_sh_
- is independent of x for up to ±10 mm changes in x direction (Figure 4b). Consequently, employing two orthogonally placed rectangular cavities can be used to measure the beam’s transverse position.
Dielectric loaded off-center cavity geometry optimization
3.2
While the off-center rectangular cavity operating in the TM110 mode provides smaller transverse dimensions compared to traditional designs, its dimensions still remain large. Leemann (21) proposed that the resonant frequency can be lowered by placing two metal rods along the axis, with gaps between the rods and the cavity wall on one side. The fundamental principle of this methodology lies in its concentration of the resonant electric field within the interstitial regions between the rod elements, thereby inducing a dual effect of enhancing cavity capacitance while reducing resonant frequency.
However, the aforementioned approach fails to achieve adequate field concentration within the gaps, thereby restricting the possibility of further dimensional reduction in the cavity structure. Given that the electric field of the TM110 mode is most intense along the central axis of the cavity, introducing dielectric material can further lower the resonant frequency (22, 23). As illustrated in Figure 5, two pairs of metal rods are connected to metal trays designed to hold dielectric disks. Additionally, the resonant frequency can be finely tuned by adjusting the dimensions of the metal rods or trays.
Off-center rectangular cavity model filled with dielectric. (a) Structure of the cavity (b) Metal rod, tray, and dielectric.
Two crucial parameters significantly influence performance: 1) the gradient of the normalized shunt impedance along the beam pipe, which directly affects the BPM’s positional resolution, and 2) the frequency sensitivity, i.e. the change in frequency per change in the thickness of the dielectric disk, denoted as t. Following optimization, the cavity’s transverse dimensions are established at 500 mm×250 mm, with a longitudinal length of 85 mm. The chosen dielectric material is 99.5% pure alumina ceramic, which has a dielectric constant of ϵ= 9.8 and exhibits a low dielectric loss of less than 0.0001. Since the cavity does not include a tuner, it is critical to maintain the frequency sensitivity within 0.5 MHz per 0.1 mm to minimize frequency shifts. After optimization, the final parameters have been determined as follows: r 1 = 15 mm, r 2 = 28 mm, and t = 11.1 mm.
Beam induced electromagnetic field within cavity
3.3
The electromagnetic field behavior excited by the passing beams within the cavity was analyzed using CST software, as depicted in Figure 6. Figure 6a illustrates the electric field distribution in the y-z cross-section, while Figure 6b presents the magnetic field distribution in the x-y cross-section. Due to the presence of the dielectric disk, the electric field of the operating mode exhibits incomplete longitudinal concentration, with negligible components existing in the transverse direction, while the magnetic field is predominantly distributed transversely. Therefore, the operational mode of this dielectric-loaded off-axis rectangular cavity BPM can be categorized as a quasi-TM mode.
Electromagnetic field distribution of operation TM110 mode (a) E-field @ side view (b) H-field @ front view.
Figure 7 presents the map of the normalized shunt impedance (R/Q) near the center of the beam pipe. Within a ±15 mm range around the pipe’s center, the contour lines are approximately parallel to the x-axis. This observation indicates that when the beam moves laterally within this region, the amplitude of the BPM output signal is predominantly influenced by the beam’s displacement in the y direction, with minimal crosstalk between the x and y axes. The actual operation includes variations in pulse duration. However, the output signals of the BPMs primarily depend on the normalized shunt impedance. Consequently, these minor alterations in proton pulse structure only affect the average beam amplitude without compromising the positional information accuracy. Although the contours curve slightly at the edges of this region, potentially introducing some crosstalk, it is not anticipated to be a significant concern, as most protons are expected to traverse the central area where the contours are primarily straight. By normalizing for beam intensity, a pair of orthogonally arranged cavities can accurately determine the beam’s transverse position.
Normalized shunt impedance map within beam pipe center of ±15 mm with the cavity that has the dielectric.
This paired BPM configuration allows for precise beam energy verification through phase analysis of the BPM signals. In the HUST-PTF facility, two critical proton energy parameters require continuous monitoring: the cyclotron’s nominal output energy (E_0_) and the clinical treatment energy (Ec).
Theoretically, the cyclotron’s design output energy remains invariant, serving as the baseline for subsequent degrader adjustments to achieve the prescribed proton energy for therapeutic applications. However, variations in accelerator operating conditions, particularly phase fluctuations in the RF accelerating field, may induce deviations in the cyclotron’s output energy. Such energy deviations can be quantitatively characterized by examining the phase correlation between the BPM signal and the cyclotron’s RF accelerating field.
During clinical treatment, the degrader controls the therapeutic proton beam energy through precise mechanical adjustment. Nevertheless, intrinsic limitations in the degrader’s calibration accuracy may lead to discrepancies between the achieved proton energy and the prescribed clinical value. The paired BPM system offers comprehensive real-time monitoring capability for the delivered clinical beam energy. Considering that therapeutic proton energies operate in the non-relativistic domain (70–230 MeV), their velocity exhibits a well-defined energy dependence. Continuous real-time energy monitoring is accomplished by precisely measuring the time-of-flight (TOF) interval between successive BPM signals as the proton beam traverses the paired detector system. For instance, with a 1 m center-to-center separation between BPMs, the measured TOF is 9.1049 ns at 70 MeV, decreasing to 5.5946 ns at 230 MeV, thereby providing reliable energy verification during therapeutic beam delivery.
Fabrication and offline testing of the cavity
4
Fabrication cavity
4.1
A prototype cavity was designed and fabricated for proof of principle, and stainless steel was chosen for the majority of its components to reduce cost. Using copper in constructing a real cavity BPM is expected to improve performance.
To enable precise tuning of the resonance frequency, the cavity was initially designed with a resonant frequency of 147.45 MHz, and its key components were intentionally manufactured slightly oversized to accommodate fine adjustments. Following the machining of the essential components of the rectangular cavity, a temporary assembly was constructed using fixtures for measurement purposes, as depicted in Figure 8. A network analyzer was employed to measure critical parameters, including the resonant frequency. This arrangement facilitated the accurate assessment and optimization of the cavity’s performance before the final assembly was completed.
Pictures of the cavity before final assembly and measurement setup. (a) components of the cavity (b) measurement setup.
To tune the resonant frequency to 146 MHz, we adjusted the small metal rods within the rectangular cavity. According to the CST simulation results presented in Figure 9, reducing the radius of these metal rods lowers the resonant frequency of the operating mode. Therefore, we decreased the rod radius by increments of 0.05 mm. Following each adjustment, we temporarily reassembled the cavity with fixtures to measure its resonant frequency. Once the frequency consistently stabilized at 146 MHz, we welded the cavity to ensure stability and performance.
Effect of metal rod radius r 1 on the resonant frequency.
Figure 10 depicts the welded rectangular cavity BPM, now operating at the frequency of 146.06 MHz. Figure 11 displays the results of the S-parameter measurements. The unloaded quality factor Q_0_ of the cavity was measured at 780.2, exhibiting a 14.6% deviation from the designed specification of 913.4. Meanwhile, the external quality factor Q_ext_ demonstrated superior performance with a measured value of 1761, surpassing the design target by 17.4%. These measurement discrepancies primarily originate from machining tolerances exceeding acceptable limits, manifesting as microscopic surface irregularities on the internal wall surfaces. Notably, since this prototype cavity is primarily intended for proof-of-concept validation, the machining precision and material selection were not rigorously controlled to reduce development costs. Consequently, certain measurement parameters exceeded the initially specified tolerance limits but remained within permissible operational margins, without compromising the cavity’s functional integrity.
Picture of the assembled rectangular cavity (dimensions: x×y×z=500×250×85 mm).
S-parameter measurement of the cavity. (a) S21 measurements (b) S11 measurement.
Measurement of normalized shunt impedance
4.2
The output signal amplitude of the BPM cavity is primarily determined by the normalized shunt impedance along the beam direction. Therefore, accurate measurement of this impedance is critical for evaluating the cavity’s performance characteristics. However, the introduction of dielectric material at the cavity’s center introduces electromagnetic field components in both longitudinal and transverse directions, which significantly compromises the measurement accuracy. Traditional cylindrical and spherical perturbators exhibit inherent limitations in achieving directional electric field modulation along the axial axis. To address this issue, a birdcage perturbation device (24) has been engineered to induce controlled perturbations in the axial electric field. This device employs metal wires to specifically perturb the electric field along their alignment, enhancing the measurements’ resolution and sensitivity. Extensive details regarding the operational mechanism of the device are elaborated in the cited works (25). Figure 12a illustrates the birdcage perturbation device, consisting of a plastic disk with a 5.5 mm radius to hold wires (26, 27). Metal wires with a 0.5 mm diameter and 10 mm length are symmetrically positioned around a circumference that measures 5 mm in radius surrounding the disk. After calibrating, the number of wires was set to 12. This configuration induces controlled perturbations in the cavity’s electric field, enabling high-precision shunt impedance measurements.
Normalized shunt impedance measurement using birdcage perturbance. (a) birdcage schematic (b) measurement setup (birdcage inside the cavity not depicted in the figure; its position can be precisely adjusted by up and down position controllers).
An automated test bench has been built to measure the electric field within the cavity. This bench incorporates the birdcage perturbation device, which is driven by a stepper motor to traverse along the central axis of the beam pipe, as depicted in Figure 12b. The change in frequency directly depends on the distance of the birdcage along the beam pipe, and the resulting deviation frequency, Δf, is recorded at various positions. For enhanced accuracy, ten measurements are taken at each position, and the average deviation frequency at the reference position is calculated to minimize measurement uncertainty, as shown in Figure 13. The calculated normalized shunt impedance at the beam pipe position was found to be 9.45 Ω.
Measured frequency deviation with respect to the distance of the birdcage along the beam pipe.
Beam simulation measurement
4.3
Using the wire displacement method, beam simulation results for the cavity were conducted on the automated test bench, as illustrated in Figure 14. Initially, a single thin metal wire was stretched through the center of the beam pipe. A 146 MHz sine-wave signal was then introduced into the cavity from an RF signal generator to simulate the transient response of the proton beam transition. The resulting induced voltage signal from the pickup within the cavity was subsequently extracted to an oscilloscope, allowing observation of the EM field distribution in both the time domain and frequency domain. The transverse position of the metal wire is scanned at constant RF signal generator output. The amplitude of the RF signal generator’s output is maintained constant while the transverse position of the metal wire, relative to the center of the beam pipe, is varied to simulate different transverse beam offsets. The wire is maneuvered over a range of ±15 mm with a displacement accuracy of less than 0.005 mm. For each position of the metal wire, the amplitude of the output signal is recorded. The measured results are depicted in Figure 15, exhibiting excellent spatial correlation with the two-dimensional distribution of the cavity’s normalized shunt impedance obtained via computational simulations.
Beam measurements with signal introduced by a wire. (a) Measurement setup (b) Measured signal.
Map of measured normalized output signal relative to the transverse positions of wire.
Output signal dependence on energy
4.4
In practice, the dielectric-loaded off-center rectangular cavity BPM is strategically positioned immediately downstream of a reference cavity BCM, so the output of the BPM can be normalized by the BCM signal, assuming the same beam current traverses both devices. Our offline test data encompassed beam positions in the range of x= ± 10 mm and y= ± 10 mm, which is more than the maximum expected variation in the beam position.
The energy of the clinical proton beams typically spans from 70 MeV to 230 MeV, which impacts the output signal of the BPM used to track the beam’s position. Simulations show that a 70 MeV proton beam exhibits a transit time factor of 0.962, and the beam current is 0.35 nA in our machine. As it passes through the cavity BPM at different lateral positions, the output signal amplitude varies between 18.68 nV and 28.52 nV. The position sensitivity of the BPM at this energy is 0.49 nV/mm. At 230 MeV, the simulation shows a transit time factor of 0.985, and the beam current is 5 nA in our machine. This increased energy and current result in a larger output signal amplitude ranging from 650.79 nV to 993.13 nV at different lateral positions. The position sensitivity at this energy level is higher, at 17.12 nV/mm. These variations in output signal amplitude and position sensitivity at different proton beam energies need to be characterized for the proper operation of the BPM.
Figure 16 illustrates the simulated amplitude of the BPM output signal at various transverse positions for proton beams at both 70 MeV and 230 MeV. This data highlights the critical need for energy-specific calibration of the BPM.
Comparison of measured output signal from the cavity BPM. (a) E=70 MeV, I=0.35 nA, (b) E=230 MeV, I=5 nA.
Crosstalk between x and y
4.5
The x-y directional coupling characteristics of the BPM output signal were experimentally studied. The experiments employed a stationary measurement approach: First, the beam position was fixed along the y-axis, and the output signal at x=0 was established as the reference baseline. We acquired normalized voltage response curves for x-directional displacements (Δx=−10~+10 mm) relative to the reference point. By calculating the normalized relative deviation δ(Δx)=|V(Δx)−V_0_|/V_0_×100% for each displacement, we quantified the coupling effect. The use of orthogonally aligned BPMs enables concurrent measurement of beam signals in the x- and y-directions, resulting in a consistent x-y coupling variation along the x-axis.
Figure 17 shows that as the beam moves along the y-axis, there is an increase in the coupling between the x and y directions. However, within ±10 mm of the center of the pipe—a typical range of operation—the output signal error due to this x-y coupling remains within 0.5%. This level of error is acceptable, especially when considering the BPM’s resolution requirement of 0.5 mm.
The maximum change in measured signal (%) over +/- 10 mm comparing to the central axis relative to y-position due to crosstalk.
Beam position measurement accuracy evaluation
4.6
The position measurement accuracy of the cavity BPM is determined by two principal factors: the position signal sensitivity and x/y directional coupling effects. Experimental characterization of the prototype BPM confirm that, under clinical operating conditions, the output signal amplitudes attains the nanovolt scale (~nV). These nanoscale signals are vulnerable to be obscured by noise sources several orders of magnitude stronger, necessitating the use of lock-in amplification methodology for reliable signal retrieval. This technology with phase-sensitive detection to extract signal components at specific reference frequencies and phases while suppressing noise at other frequencies.
An SR844 model lock-in amplifier is used for evaluating the position measurement accuracy of this prototype BPM (for technical specifications and operating procedures, refer to the instrument manual). Performance evaluation was conducted at five characteristic energy points across the proton therapy energy range (70–230 MeV), with quantitative results shown in Table 4. The measured position accuracy demonstrates energy dependence, ranging from 0.65 mm at 70 MeV to 0.02 mm at 230 MeV. Notably, the cavity BPM maintains sub-0.5 mm accuracy throughout most of the therapeutic energy spectrum.
Additional measurements reveal that when the beam deviates within ±10 mm from the central axis, x/y directional coupling induces output signal errors less than 0.5%. These results indicate that the fundamental limitation in positional measurement accuracy stems principally from the resonant cavity’s intrinsic sensitivity characteristics.
While the current prototype utilizes cost-effective stainless steel fabrication for proof-of-principle validation, this material selection inherently constrains its detection sensitivity. Substantial performance enhancement is theoretically achievable through precision-engineered copper cavity BPM systems, thereby satisfying the requirements (≤ 0.5 mm) for real-time, non-intercepting beam monitoring applications.
Conclusion
5
This paper introduces an innovative cavity BPM design tailored to overcome the challenges associated with monitoring low-intensity, low-frequency clinical proton pulses, typical in cyclotron-based proton therapy systems. These systems frequently use an energy degrader to regulate beam energy, complicating real-time diagnostics due to the low beam current. Traditional cavity BPMs, which typically operate in higher modes, face limitations under such conditions. Operating in higher modes leads to weaker electromagnetic field excitation inside the cavity, reducing the sensitivity needed to detect low-current beams. Additionally, these cavities’ large transverse dimensions, necessary to match the low repetition rates, render them impractical for some clinical applications.
To overcome the limitations of traditional designs, our novel cavity BPM features an off-center rectangular resonant cavity operating in the TM110 fundamental mode. This innovative configuration significantly enhances detection sensitivity. Additionally, the cavity is filled with alumina ceramic, which increases the equivalent capacitance and lowers the resonant frequency, enabling a more compact and efficient design. As a result, the transverse dimensions of the cavity have been drastically reduced from the conventional 4236×2118 mm to a streamlined 500×250 mm, while maintaining exceptional performance.
Conventional BPMs, including ionization chambers and fluorescent screens, achieve high-precision beam position measurement. Nevertheless, these interceptive devices necessitate physical insertion of detection materials into the beam path, resulting in inevitable beam perturbation. Specifically, fluorescent screen BPMs require complete beam interception, restricting their application exclusively to beam commissioning procedures. By comparison, resonant cavity BPMs offer non-intercepting online beam position monitoring while maintaining uninterrupted beam transmission, with the additional capability of concurrent real-time proton beam energy verification.
The prototype cavity BPM has undergone comprehensive cold tests using a network analyzer. These tests indicate that the novel cavity BPM can detect proton beams with energies from 70 to 230 MeV. Measurements demonstrate energy-dependent sensitivities of 0.49 nV/mm at 70 MeV and 17.12 nV/mm at 230 MeV and with less than 0.5% crosstalk between the x and y directions over ±10 mm. Within the therapeutic energy range (70–230 MeV), experimental measurements confirm that the energy-dependent beam position accuracy remains within 0.5 mm, with the exception observed at the lowest energy point.
The performance of the novel cavity BPM is anticipated to be significantly enhanced upon realization of a fully functional prototype, thereby offering an effective technical approach for real-time, online monitoring of therapeutic proton beams.
The reference list from the paper itself. Each links out to its DOI / PubMed record.
- 1Schippers JMDölling R Duppich J Goitein G Jermann M Mezger A. The SC cyclotron and beam lines of PSI’s new proton therapy facility PROSCAN. Nucl Instruments Methods Phys Res B. (2007) 261:773–6. doi: 10.1016/j.nimb.2007.04.052 · doi ↗
- 2Mohan R. A review of proton therapy–Current status and future directions. Precis Radiat Oncol. (2022) 6:164–76. doi: 10.1002/pro 6.1149 PMC 949903636160180 · doi ↗ · pubmed ↗
- 3Lee SB. Proton therapy review: proton therapy from a medical. Prog Med Phys. (2020) 31:99–110. doi: 10.14316/pmp.2020.31.3.99 · doi ↗
- 4Qin B Liu X Chen Q-S Li D Han W-J Tan P. Design and development of the beamline for a proton therapy system. Nucl Sci Tech. (2021) 32:138. doi: 10.1007/s 41365-021-00975-y · doi ↗
- 5Li P Li D Qin B Zhou C Han W Liao Y. Design of HUST-PTF beamline control system for fast energy changing. Nucl Eng Technol. (2022) 54:2852–8. doi: 10.1016/j.net.2022.02.023 · doi ↗
- 6Mei Z Fan K Liang Z Yang J Fan M. Optimization of a B 4C/graphite composite energy degrader and its shielding for a proton therapy facility. Nucl Inst Methods Phys Res A. (2021) 995:165127. doi: 10.1016/j.nima.2021.165127 · doi ↗
- 7Chen A Chen Q Liu X Zhou C Li D Qin B. Prototype development of the beam diagnostic system of a proton therapy facility based on a superconducting cyclotron. Nucl Inst Methods Phys Res A. (2021) 998:165208. doi: 10.1016/j.nima.2021.165208 · doi ↗
- 8Guo HD Hu YY Li XY Lin YJ Tan P Yu Y. The optimization design and output characteristic analysis of ionization chamber dose monitor in HUST-PTF, IBIC 2017. Grand Rapids MI, USA: JA Co W. (2018). doi: 10.18429/JA Co W-IBIC 2017-WEPCF 09 · doi ↗