Patent Description:
Currently, most external radiotherapy treatments use photons to irradiate tumors. However, hadron therapy (using protons or carbon ions) damages tumor cells more effectively than photon therapy.

Charged particles have an inverse depth-dose distribution in comparison to photons, delivering a dose increasing with penetration depth up to a maximum at the end of the particles path (Bragg peak). This maximizes the dose transmitted to the cancerous area and reduces the dose transmitted to the healthy tissue.

Heavy ions such as carbon ions additionally show an increased Relative Biological Effectiveness (RBE). The RBE is defined as the ratio of the irradiated dose of ions to that of a reference photon energy that would be required to result in the same biological effect for both. To ensure a safe dose delivery and to fully take advantage of ion therapy, a reliable estimation of the RBE of the ion beams is required. A Microdosimetric Kinetic Model (MKM) may be used to predict the RBE of ion beams, based on microdosimetry, which rely on measurements of stochastic energy-deposition distributions in micro-sensitive volumes comparable in size to a human cell.

In routine clinical proton therapy, a constant RBE value of <NUM> is usually assumed. However, the RBE has been shown to vary with different Linear Energy Transfer (LET) values.

The LET is used to describe the average energy deposited per unit length (in keV/µm) in an absorber material. Limitations of the LET for precise assessment of the RBE have resulted in the development of a set of measurable stochastic quantities, such as the lineal energy which provides the fundamental basis for microdosimetry.

The lineal energy is used to describe the energy deposited by a single event, namely ε, in a micron-size sensitive volume, or microvolume, along the mean particle track length, l, which is given by: <MAT>.

Several devices such as the tissue equivalent proportional counter (TEPC) or silicon-based semiconductor microdosimeter may be used for the measurement of microdosimetric spectra. Known TEPC consist of a tissue equivalent plastic sphere in a grounded aluminum shell. The sphere is filled with a tissue equivalent gas to simulate interactions with human tissue. This kind of detectors usually use centimeter-sized sensors, which is much larger than the size of a typical human cell.

Mini-TEPCs have been developed with cylindrical sensitive volumes having sizes of the order of a few tens of millimeters. Recently, different miniaturized tissue-equivalent gas detectors corresponding to operation at a nanometric level down to <NUM> have been developed for microdosimetry applications in radiotherapy.

TEPC detectors have had some success while tested in different therapeutic heavy ion beams but are still being further developed. Currently, to the knowledge of the inventors there is no commercial product and the construction of a mini-TEPC is a demanding operation requiring special knowledge and maintenance during use, e.g. for the supply of gases.

Limitations of TEPCs compared to microdosimetry include the need for high-voltage and for a gas supply system. Further limitations include so-called pulse pile-up problems, as well as a low spatial resolution due to a relatively large size of the sensitive volumes compared to other solid-state microdosimeters (which are in the µm size range).

Silicon-based microdosimeters, better known as silicon-on-insulator (SOI) microdosimeters, have also been developed over the last <NUM> years. Different generations of SOI devices have been designed.

The use of SOI microdosimeters in lineal energy measurements offers high spatial resolution and counting rates at low costs. Using the latest generation of silicon-based microdosimeters, a good agreement with the results from the well-established TEPCs was achieved.

However, a frequently raised issue is the question of tissue equivalence in the case of silicon (with Z = <NUM>), leading to complex correction factors when compared to other materials such as diamond (Z = <NUM>). Silicon-based sensors are therefore not optimal in this respect.

Diamond, with its unique physical properties (e.g. a large-band gap, temperature stability, fast drift velocity and low capacitance), has been identified as a promising candidate material to produce microdosimetry devices. Recently, significant developments in diamond-based microdosimetry have been made with various fabrication and operational approaches.

However, no known micro-dosimeters are completely satisfactory to fulfill all requirements for radiation Quality Assurance in hadron therapy.

Most of known micro-dosimeters need an additional dosimeter or Monte Carlo (MC) simulations for the verification of the dose. Therefore, the average absorbed dose (dose-depth profile) of the ion beams in water is measured using different commercially available tools in a separate run where conditions are assumed to be the same as for the micro-dosimetric run. These additional tools are placed at the same effective depth within a water phantom as the micro-dosimeters (along the central axis of the beam) to obtain a depth-dose profile of the beam and verify the quality of the measured micro-dosimetric spectra. In addition to the physical measurements of the absorbed dose, as mentioned above, Monte Carlo simulations of the entire clinical beamlines are made and used for the verification of the ion beam range.

The publication "<NPL> concerns a so-called 3D lateral electrode structure (3D-LES) diamond-based detector prototype.

The publication "<NPL> discloses a single-crystal CVD diamond detector prepared for high-temperature operation.

The publication "<NPL> relates to a diamond-based microdosimeter prototype comprising wall-less micro-sensitive volumes.

A system based on a Si-based MOSFET (Metal-Oxide-Semiconductor Field-Effect) transistor) allowing the simultaneous measurements of the absorbed dose and the micro-dosimetric spectra is disclosed in the publications <NPL>) and <NPL>).

The detector operates by collecting free charge produced by ionizing radiation in the depletion layer. The latter is extended by reverse biasing of the p-n junction, which is connected to a spectroscopy set up. A pulse-height spectrum of ionized radiation can be acquired, i.e. a micro-dosimetric spectrum.

The electric signal used for the integral dosimetry measurement with the MOSFET detector is the threshold voltage of the transistor, which exhibits a shift after irradiation. This radiation induced effect must be removed by annealing at <NUM>-<NUM> after a few measurements.

The MOSFET detector can be simultaneously used for integral dosimetry of radiation dose and for differential spectroscopy.

However, the response of the MOSFET detector is strongly dependent on the particle LET angle with respect to the oxide electric field and to temperature.

A further significant limitation of this system is also the measurement of the lineal energy, because due to a high noise level, no lineal energies measurements below some level are possible.

Most important, the MOSFET's shift in threshold voltage requires as mentioned above a thermal treatment to reset the device and is not very practical. Also, after several irradiations the detector suffers permanent damage and cannot be re-used.

There thus exists a need to obviate the drawbacks of known systems for micro-dosimetry and benefit from a reliable system allowing an accurate simultaneous measurement of the absorbed dose and the micro-dosimetric spectra.

The present invention relates to a system according to claim <NUM> for dosimetric and micro-dosimetric ionizing radiation characterization, comprising:.

The picoammeter enables low DC current measurements corresponding to the dose rate (current at the plateau) and dose (integrated current).

The invention allows precise and accurate measurements of lineal energy spectra in the form of a calibrated pulse-height spectrum, which provide an essential input parameter, such as dose-mean lineal energy, for the calculation and thus prediction of the RBE for a specific cell type in in compliance with the MKM model.

The invention allows for example an 'in-flight' scan of the radiation field to get dose profiles, i.e. in 3D, then to identify 'points of interest' and measure microdosimetric spectra.

This dual measurement of dose rate and dose is made with a same sensor and is particularly useful for ion beam characterization in hadron therapy, as the knowledge of the lineal energy provides information about the effectiveness of the ion beam, while the dose rate may be used for the verification of the range of the ion beam and may help position the sensor within the irradiation field with high precision, which contributes to Quality Assurance (QA) improvement as well as radiobiological optimization of the treatment plans.

The invention allows the fabrication of a compact and user-friendly system with the ability to measure both quantities above with high spatial resolution at low noise and with the same sensor in a reliable manner. Furthermore, the sensor allows "pinpoint" measurements, for example within an area less than <NUM><NUM>, better less than <NUM><NUM>, for example about <NUM><NUM>. Accordingly, the system gives little perturbation to the field at the point of measurement, improving the precision and the reliability of such measurements.

In addition, thanks to the wide band gap of diamond the system has ability of measuring very low induced current signals. The sensor may exhibit a small leakage current, that may be in the order of <NUM>. 01pA or less, and a high sensitivity threshold for lineal energy, that may be of the order of <NUM> keV/µm (calculated for water equivalent) or less.

Moreover, due to the diamond physical properties, the sensor is more tissue equivalent and radiation hard when compared to the silicon-based sensors.

At last, no annealing is required to reset the sensor between two consecutive measurements.

In some embodiments, the diamond-based sensor comprises at least two micro-sensitive volumes having respective electrodes, the at least one micro-dosimetric readout channel and the at least one dosimetry readout channel being connected to these respective electrodes.

In some other embodiments, the at least one micro-sensitive volume is connected to top and back electrodes, the at least one micro-dosimetric readout channel and the at least one picoammeter being connected respectively to these top and back electrodes, or vice-versa. A bias voltage may be applied to the top electrode or to the back electrode through the picoammeter.

In some other embodiments, the at least one micro-dosimetric readout system and the at least one dosimetry readout channel are connected to a same electrode, preferably a top electrode. The charge sensitive amplifier may be connected to the corresponding electrode through a decoupling capacitor.

When a bias voltage is applied, it may range from <NUM> to <NUM> V or more, so that the electric field induced by the bias voltage is for example of the order of 10V/micron.

Preferably, the sensor comprises a non-electrically active material extending around said at least one micro-sensitive volume.

In the context of the invention, a "non-electrically active material" refers to a material that creates substantially no directional drift of radiation-induced free charge carriers under an electric field. While incident radiation such as an ion beam may create free charge carriers in the non-electrically active material, the lifetime of the free charge carriers in the non-electrically active material is very short, e.g. on the order of a picosecond.

As a result, under typical conditions, e.g. under electric fields of <NUM>-<NUM> V/µm, no measurable signal is generated in the non-electrically active material.

Examples of suitable non-electrically active materials include radiation hard resists such as epoxy-based resins (e.g. SU-<NUM>), polymers such as PMMA, and some inorganic materials such as glass.

The non-electrically active material may have a planar configuration and/or be of a substantially constant thickness, preferably having a same thickness as the micro-sensitive volumes.

The non-electrically active material preferably extends in contact with and around the entire periphery of each one of the micro-sensitive volumes.

Preferably, the non-electrically active material fills all the space between the micro-sensitive volumes, leaving no voids between them.

The non-electrically active material may be rigid or flexible.

The micro-sensitive volumes may be mechanically supported by the non-electrically active material, and the latter may be supported only at its periphery by a frame, preferably a diamond-based frame made of a same material as the micro-sensitive volumes.

The non-electrically active material may support metal electrodes that covers both the micro-sensitive volumes and the non-electrically active material.

The non-electrically active material may support a doped layer or cover a doped layer.

The non-electrically active material may be superposed entirely to a substrate, for example a HPHT (high pressure high temperature) or CVD diamond substrate.

The non-electrically substrate may support conductive tracks extending along its thickness.

The sensor comprises at least one micro-sensitive volume, preferably an array of micro-sensitive volumes.

The micro-sensitive volume may have a cylindrical shape, preferably with a symmetry of revolution. In some variants, the micro-sensitive volume has a hemispherical or spherical shape.

A thickness of the micro-sensitive volume may range from <NUM> to <NUM>, better from <NUM> to <NUM> and in particular from <NUM> to <NUM>.

A diameter or largest dimension in cross-section of the micro-sensitive volume may range from <NUM> to <NUM>, better from <NUM> to <NUM>, even better from <NUM> to <NUM> or <NUM> to <NUM>.

The volume of one micro-sensitive volume may range from <NUM><NUM> to <NUM><NUM>, better from <NUM> to <NUM> and even better from <NUM> to <NUM><NUM>.

The micro-sensitive volume is preferably made of Single Crystalline Chemical Vapor Deposited (scCVD) diamond.

A top electrode connected to the dosimetry and/or micro-dosimetry readout channel(s) may interconnect several micro-sensitive volumes of an array of micro-sensitive volumes of the sensor. The number of interconnected micro-sensitive volumes may range from <NUM> to several thousands.

The number of micro-sensitive volumes of the sensor may range from <NUM> to several thousands.

At least some micro-sensitive volumes, preferably all micro-sensitive volumes, are surrounded by said non-electrically active material where no directional charge drift under the presence of electric field takes place.

In some variants, the micro-sensitive volume is surrounded by a Guard Ring (GR) electrode, as disclosed in <NPL>). Such a sensor is referred to below as the "GR sensor".

The micro-sensitive volumes may also be defined by a boron-doped diamond deposited on top of intrinsic diamond as in the so-called self-biased "p+ sensor" disclosed in the publication "scCVD diamond membrane based microdosimeter for hadron therapy", IA Zahradnik, MT Pomorski, L De Marzi, D Tromson, P Barberet, N Skukan,. Physica Status Solidi (a) <NUM> (<NUM>), <NUM>.

All micro-sensitive volumes of the sensor may be of a same thickness, or in a variant of different thicknesses.

Micro-sensitive volumes of different thicknesses may be connected to respective readout channels.

The micro-sensitive volumes may have end faces in contact with respective top and back electrodes.

The terms "top" and "back" refer to one orientation of the sensor. The sensor may be used in any appropriate orientation with respect to the incident radiation, and the top electrode may or not be facing the incident radiation.

A micro-sensitive volume may be in contact or not with a doped layer, for example a p or p+ type or n or n+ type doped layer, preferably a p+ doped layer or a n+ doped layer, for example a p+ boron doped layer or a n+ phosphorus doped layer.

The electrodes may be metal based or carbon-based electrodes. An electrode may be constituted at least partially by a doped layer.

The system preferably comprises processing means for generating a Lineal Energy Spectrum (LES) based on signals outputted by the at least one micro-dosimetric readout channel, and preferably also an RBE based on said lineal energy spectrum.

The system preferably comprises processing means for integrating the dose rate signal provided by the picoammeter and generate dose data.

The processing means may comprise any computer such as a personal computer or specialized hardware such as microcontroller or FPGA circuit. The processing means may comprise any interface for signal processing, for example Multi Channel Analyzer, A/D converter, filters, amplifiers, etc..

The invention also relates to a method according to claim <NUM>, for assessing the dose and lineal energy spectra of an ionizing radiation, comprising measuring the dose rate and the deposited energy distribution using a system as defined above. This measurement may be performed simultaneously and with a same sensor, each with at least one micro-sensitive volume connected to micro-dosimetric and dosimetric readout channels or with at least two different micro-sensitive volumes connected respectively to a micro-dosimetric readout channel and to a dosimetric readout channel. The sensor may be placed after a water or plastics phantom or within a water phantom.

The ionizing radiation may be a hadron therapy ion beam, for example a proton beam or a beam of heavier ions such as carbon ions. The ion beam may be produced by Pencil Beam Scanning (PBS) or by passive scattering (so-called double scattering (DS)) delivery techniques.

The method of the invention is also useful when the ionizing radiation is space radiation.

The system <NUM> shown in <FIG> comprises a diamond-based sensor <NUM> and two readout channels <NUM> and <NUM> for respective micro-dosimetric spectrum and dosimetry measurements.

The sensor <NUM> defines an array of micro-sensitive volumes <NUM> that are each responsive to an incident ion beam.

These micro-sensitive volumes <NUM> are preferably made of scCVD diamond and extend between top electrodes, two of them (being referred to as <NUM> and <NUM>) being shown in the Figures, and a back electrode <NUM>, which may be metallic or made by other materials such as carbon-based materials for example.

Each top electrode <NUM> or <NUM> may contact a respective set of micro-sensitive volumes <NUM> arranged in an array, as shown. In a variant (not shown), each top electrode contacts only one respective micro-sensitive volume <NUM>.

A non-electrically active material <NUM> such as an epoxy-based resist or PMMA, may extend around each micro-sensitive volume <NUM>, as shown, to improve the performances of the sensor <NUM> by isolating each micro-sensitive volume from charge diffusion from the neighboring material.

Each micro-sensitive volume <NUM> may be of a cylindrical shape with a diameter in the range <NUM>-<NUM> microns for example, and a thickness no greater than <NUM> microns.

The back electrode <NUM> is connected to all micro-sensitive volumes <NUM>.

This back electrode <NUM> may be connected by a connection <NUM> to a bias voltage source.

The top electrode <NUM> is connected to a first readout channel <NUM> for micro-dosimetry measurement. The other top electrode <NUM> is connected to a second readout channel <NUM> for dosimetry measurement.

Other top electrodes (not shown) may be connected similarly to corresponding readout channels (not shown).

The first readout channel <NUM> comprises a Charge Sensitive Amplifier (CSA) <NUM>, known per se, which outputs a voltage based on the integration of the current induced by a single passing particle through a corresponding volume at the input. The integration time is typically very short here, below 1ns.

The CSA is connected to a Multi-Channel Analyzer (MCA) which may further amplify and digitize the signal. The latter may be, as shown in <FIG>, a pulse <NUM> and the processing may result in generating for a given travel distance in a phantom, such as a water phantom or a plastics phantom, a pulse height spectrum <NUM> figuring the number of counts (as ordinate) with respect to the Energy (as abscissa).

These generated pulse-height spectra may then be calibrated with energy and converted to lineal energy spectra <NUM> which allows to calculate for each depth (position in the Bragg curve) the dose-mean lineal energy and allows to estimate the cell specific RBE in compliance with the MKM model, as disclosed for example in <NPL>).

The second readout channel <NUM> comprises a picoammeter <NUM> that measures the DC current induced by the beam in the sensor <NUM>. A relative dose rate <NUM> may be estimated at the measured curves plateau. The integration of this current curve results in a measured collected charge and provides the information <NUM> about the dose.

The micro-dosimetric spectrum <NUM> provides information allowing to compute the dose-mean lineal energy to estimate the cell specific RBE in compliance with the MKM model, as explained above, while the simultaneous measurement of the dose may be used additionally for the verification of the 3D dose profiles, and the position of the sensor within the irradiation field with high precision (dosimetry).

The picoammeter <NUM> of the embodiment of <FIG> may be connected to ground GND, as illustrated in <FIG>.

<FIG> shows in more details a possible structure for the sensor of <FIG> and <FIG>, where the array of single solid-state micro-sensitive volumes is embedded within a non-electrically active material. This sensor is referred to as "fully 3D sensor".

The invention also works with other types of diamond-based sensors, such as the "GR sensor" or "p+ sensor" mentioned above.

The layer of non-electrically active material <NUM> may be supported by a frame <NUM> as shown.

This frame <NUM> may support bonding pads <NUM> and <NUM> connected to respective top electrodes, as shown, and to the readout channels.

The sensor <NUM> of <FIG> may be microfabricated as illustrated in <FIG>.

Firstly, a diamond plate <NUM> is provided (<FIG>). The diamond plate is preferably between <NUM> and <NUM> thick and may be made of single crystal chemical vapor deposition (scCVD) raw synthetic diamond.

As shown in <FIG>, the diamond plate <NUM> is then sliced in thin plates <NUM> with a preferred thickness of <NUM> to <NUM>, and polished. The surface area of the thin plates may be comprised between 3x3 mm<NUM> and <NUM>×<NUM><NUM>.

Next, the thin plate <NUM> is etched to create an ultra-thin membrane <NUM> with a thickness smaller than or equal to <NUM>, suspended over a bulky frame <NUM> (<FIG>). The ultra-thin membrane <NUM> may have the same surface area as the original thin plate. The bulky frame <NUM> may be U-shaped when viewed in a direction orthogonal to the plane of the membrane.

In order to obtain the ultra-thin membrane <NUM>, a deep Ar/O<NUM> plasma etching is used, following the method described e.g. in <NPL>).

The ultra-thin diamond membrane <NUM> is advantageously cleaned with hydrofluoric acid and a hot acid treatment in order to eliminate possible surface contamination.

Optionally, the sample is fixed onto a silicon wafer in order to achieve a better structural stability for the following processing steps. To do so, a thin layer of photoresist is spin coated on the silicon wafer and the sample placed on it with its top side facing up. The photoresist is then hardened by soft baking for a few minutes, for instance at a temperature of <NUM>.

In the next step, as shown in <FIG>, a positive epoxy-based resist <NUM> is deposited on the diamond membrane. Photolithographic patterning is then performed using UV light. In other words, only specific areas of the resist layer <NUM> are exposed to the UV light, such that the resist from these specific areas may be removed. This creates empty volumes <NUM> that allow a direct access to the intrinsic diamond membrane <NUM> through the resist layer <NUM>.

Next, a layer of chromium (Cr) which may be <NUM> to <NUM> thick is deposited onto the top side of the diamond membrane <NUM>. The sample may then be gently rinsed with acetone in order to detach the residual photoresist layer (lift-off technique). A metallic Cr mask <NUM> on the diamond membrane <NUM> is thus obtained (<FIG>). A wet etch approach may also be used to obtain the Cr mask <NUM>. Acetone rinsing may be used to remove the sample from the silicon wafer.

Next, as shown in <FIG>, Ar/O<NUM> Reactive Ion Etching (RIE) is carried out to create the single-standing micro-sensitive volumes <NUM> within the diamond membrane <NUM>. Due to the higher etching selectivity for diamond compared with the Cr mask <NUM>, micro-sized volumes of diamond are etched beneath the metal mask.

The diamond membrane <NUM> is not fully etched through: a residual layer <NUM> of intrinsic diamond, which may be approximately <NUM> thick, is left as a layer supporting the µSVs <NUM>.

A chromium etchant followed by a gentle hot acid cleaning treatment may then be applied to the etched membrane, in order to remove the residual Cr-mask and possible surface contamination of the sample. Isopropanol rinsing and blow-drying may be carried out. Additionally, Ar plasma may be used to ensure that the surface of the sample is clean from any organic contamination before further processing.

Next, a layer <NUM> of non-electrically active material is spin coated onto the supporting layer <NUM> as illustrated in <FIG>. The layer <NUM> may be made of a hard baked radiation hard resist or PMMA, for example an epoxy-based SU-<NUM> photoresist.

To limit the layer <NUM> to regions closely surrounding the µSVs <NUM>, photolithographic patterning may be performed using UV light. In other words, only specific areas of the resist layer <NUM> are exposed to the UV light, such that the resist from these specific areas may be removed.

The following step, depicted in <FIG>, consists in removing the residual diamond layer <NUM> from the bottom side of the non-electrically active layer <NUM>. To do so, Ar/O<NUM> reactive ion etching may be used.

Then, as shown in <FIG>, the bottom electrode <NUM> which may be metal-based, preferably aluminum-based, is deposited as a large strip on the bottom side of the layer <NUM> and of the array of µSVs <NUM>. The electrode <NUM> acts as a full pad back electrode for the sensor and provides improved mechanical stability.

Finally, as shown in <FIG>, top electrodes on the top side of the layer <NUM> and of the µSVs <NUM> are deposited.

To this end, the sample may be fixed on a silicon wafer following the procedure described previously. To create multiple patterned electrodes <NUM>, <NUM>, covering only the area closest to the µSVs <NUM>, a standard resist is spin coated onto the sample. Using photolithography, resist patterns can be created which will define the top electrical contacts <NUM>, <NUM> and the bonding pads <NUM>, <NUM>.

In the case of metal-based electrodes, a wet etch technique may be applied: using a specific metal etchant, all metallization except the regions covered by the resist is removed. In the case of carbon-based electrodes, a lift-off technique may be used instead.

The sensor <NUM> is then ready for mounting onto an appropriate sensor carrier and for wire-bonding. The sensor may be integrated into a PCB with connectors (for example of the SMA type) for connection to read out electronics.

<FIG> shows a variant embodiment where the picoammeter <NUM> is connected between the back electrode <NUM> and the bias voltage source.

The CSA <NUM> is connected to the top electrode <NUM> as in the embodiment of <FIG> and <FIG>.

In this embodiment, the same set of micro-sensitive volumes <NUM> provides the signal that is read out by the first and second readout channels <NUM> and <NUM>, contrary to the embodiment of <FIG> and <FIG> where the signals come from respective sets of micro-sensitive volumes <NUM>.

In the embodiment of <FIG>, the picoammeter <NUM> is connected between the back electrode <NUM> and the ground GND. The CSA <NUM> is connected through a decoupling capacitor <NUM> to the top electrode <NUM>. The latter is connected by a connection <NUM> to a source of biasing voltage.

In the variant of <FIG>, the back electrode <NUM> is connected via a connection <NUM> to a source of biasing voltage.

The picoammeter <NUM> is connected between the top electrode <NUM> and the ground GND. The CSA <NUM> is connected through a decoupling capacitor <NUM> to the top electrode <NUM>.

In the examples shown where the readout channels are connected respectively to the top and back electrodes, there is also a possibility for reverse configuration, i.e. the readout channel connected to the top electrode is then connected to the back electrode and the read out channel connected to the back electrode is then connected to the top electrode. Such reverse configuration is however not preferred as it may worsen the signal if the electrodes are not of a similar size, causing the electric field to be inhomogeneous.

An example of experimental set-up is shown in <FIG> and <FIG>, to characterize an incident proton beam in different water phantom travel distances.

The sensor has the configuration of <FIG> and <FIG> for example, or may have any other appropriate configuration, and be for example a "GR sensor" or a "p+ sensor".

The output for the micro-dosimetric spectrum (pulse-height) measurement from one set of micro-sensitive volumes <NUM> is fed into a charge sensitive preamplifier (CSA) Amptek CoolFET [AMPTEK]. A positive bias voltage fixed to 15V equivalent to an electric field within the micro-sensitive volumes (also referred to as µSVs) of <NUM> V/µm during the entire experiment, is applied directly to the back electrode of the sensor. The positive bias voltage is established by a voltage adjustment element (VADJ).

The pre-amplified voltage pulses from the CSA, previously induced by single ionizing particles in the micro-sensitive volumes of the sensor <NUM>, are fed into a multi-channel analyzer LabZY nanoMCA II (MCA). The MCA amplifies and digitizes the signal, as well as processes the generated pulse-height spectra while communicating with a personal computer (PC) situated in the control area through a Wi-Fi network for example.

The beam induced DC current from another set of micro-sensitive volumes <NUM> of the same sensor is fed into a high precision Keithley Picoammeter (pAM) for the dose rate and depth-dose profile measurement.

In <FIG> the results are summarized. The induced current curves corresponding to the dose rate during irradiation with a <NUM> MeV proton beams for various depths in plastic water phantom are shown in a). Remarkably low leakage current values (I < < 1pA) can be observed when the proton beam is off. The relative dose rate (current at the plateau), dose (integrated current) and a rough GEANT4 simulation of the 100MeV proton beam are compared in b). A perfect agreement between both measured quantities and a good agreement with the simulated proton beam range, confirm the system's ability to measure simultaneously reliable depth-dose profile curves. Additionally, the very good agreement between the dose and dose rate indicates a possibility of fast scanning in water phantoms if only constant dose rate is guaranteed at accelerator level. Finally, in c) the calibrated micro-dosimetric spectrum for selected depth within the measured Bragg Peak are presented and exhibit typical and expected shift of their peak as well as a broader spectrum towards greater LET values. In d) the measured dose-mean lineal energy values are presented with which the RBE of a specific cell type can be estimated in compliance with the MKM model.

These results demonstrate a great performance of the system as a QA tool in the hadron therapy.

Claim 1:
A system for dosimetric and micro-dosimetric ionizing radiation characterization, comprising:
- at least one diamond-based sensor (<NUM>) comprising at least one micro-sensitive volume (<NUM>),
- at least one micro-dosimetric readout channel (<NUM>) comprising a charge sensitive preamplifier (CSA) connected to said sensor for outputting a signal representative of the distribution of the energy deposited by the ionizing radiation impacting said at least one micro-sensitive volume (<NUM>),
characterized in that said system further comprises
- at least one dosimetry readout channel (<NUM>) comprising a picoammeter (<NUM>) for reading current induced by said ionizing radiation in said at least one micro-sensitive volume (<NUM>) and generating a signal representative of a dose rate.