Device for estimating the activity of a radioactive liquid

Abstract

The invention relates to a device (1) for measuring the activity of a radioactive liquid (2), the device comprising: - a detection module (10) extending around a measurement chamber (3) which is intended to contain the liquid, the detection module being configured to detect ionising radiation and to transmit a detection signal; - a processing unit (40) connected to the detection module and programmed to estimate the activity of the radioactive liquid on the basis of the detection signal; the device being characterised in that the detection module comprises:  a solid-state scintillation detector (11) extending around the measurement chamber;  at least two photodetectors (15) optically coupled to the scintillation detector; the device comprises a capillary (3) extending around a longitudinal axis (Δ), the capillary being arranged so as to be in a measurement position, the capillary forming the measurement chamber.

Description

[0001] Description

[0002] Title: Device for estimating the activity of a radioactive liquid

[0003] TECHNICAL FIELD

[0004] The technical field of the invention is the analysis of the volume or mass activity of a radioactive liquid, in particular with a view to use for diagnostic or medical treatment purposes.

[0005] PREVIOUS ART

[0006] Some nuclear medicine applications require the introduction of a product labeled with a radioactive isotope into the body. This is also known as a radiopharmaceutical. The product may be used for medical treatment, for example, in brachytherapy. The product may also be used for diagnostic purposes.

[0007] Among the radioactive isotopes, or radionuclides, commonly used in nuclear medicine, we can cite for example 1:L C, 18 F, 67 Ga,90 Y, " m Tc, m ln, 123 L, 125 L, 131 L, 201 TI. Before injecting them into a patient's body, it is necessary to quantify their activity as accurately as possible. It may also be useful to identify and quantify the presence of any impurities resulting from the radioactive isotope production process.

[0008] In a hospital setting, the activity of an isotope is quantified prior to its injection, using a measuring device usually called an activimeter. An activimeter is a detector, generally an ionization chamber, forming a well. The radioactive product is introduced, in liquid form, into the well and its activity is estimated. The radioactive product is contained in a container, such as a syringe or a bottle. The ionization chamber has previously been calibrated, making it possible to obtain a relationship between the intensity of the current, resulting from the ionization chamber, and the activity of the radioactive isotope. The calibration depends on the type of isotope used. The calibration also depends on the geometry of the measurement, that is to say the shape and nature of the container containing the radioactive product. The calibration is, for example, different when the radioactive product is contained in a syringe or a bottle.Calibration depends on the fill level as well as the isotope to be measured. Calibration generally requires the use of a specialized laboratory.

[0009] Document US3657541 describes a device for determining the activity of a radioactive liquid intended for medical use. The inventors propose a device for estimating the volumetric, or mass, activity of a solution containing an isotope intended for use in nuclear medicine, in a simple and automated manner, without requiring the use of complex calibration.

[0010] STATEMENT OF THE INVENTION

[0011] A first object of the invention is a device intended to measure the activity of radioactive liquid, and in particular of a drop of radioactive liquid, comprising:

[0012] - a detection module, extending around a measuring chamber, intended to contain the liquid, the detection module being configured to detect ionizing radiation emitted in the measuring chamber and to emit a detection signal dependent on a quantity of radiation detected;

[0013] - a processing unit, connected to the detection module, and programmed to estimate an activity of the radioactive liquid from the detection signal; the device being characterized in that

[0014] - the detection module includes:

[0015] • a solid-state scintillator detector configured to produce scintillation photons when exposed to ionizing radiation, the scintillator detector extending around the measuring chamber;

[0016] • at least two photodetectors, optically coupled to the scintillator detector, each photodetector being configured to detect scintillation photons and generate a detection signal dependent on the quantity of scintillation photons detected; the device comprising a capillary, extending around a longitudinal axis, and delimiting an internal space intended to contain the radioactive liquid, the capillary being arranged to be placed in a measuring position, in which the scintillator detector extends around the internal space of the capillary, the capillary forming the measuring chamber.

[0017] Preferably, the scintillator detector extends around the capillary.

[0018] According to one possibility, the scintillator detector forms a wall of the capillary.

[0019] Advantageously,

[0020] - an opening is made through the scintillator detector, along the longitudinal axis; the capillary extends through the opening when it is arranged in the measuring position. Each photodetector may in particular extend around a detection axis intersecting the longitudinal axis. The respective detection axes of each photodetector are preferably coplanar, and preferably in a plane perpendicular to the longitudinal axis. The respective detection axes of each photodetector are preferably regularly angularly spaced from each other, around the longitudinal axis.

[0021] The scintillator detector may have a spherical, cylindrical, or polyhedral central portion through which the aperture passes. The device is such that the capillary is inserted into the aperture at least in the measuring position.

[0022] Each photodetector is preferably optically coupled to the scintillator detector by a flat face. The flat face is intended to promote optical coupling with the photodetector.

[0023] According to one possibility, the scintillator detector extends, from the aperture, to at least one planar face, such that the scintillator detector comprises the central portion, around the aperture, and the planar face.

[0024] Preferably, the scintillator detector has as many flat faces as there are photodetectors.

[0025] According to one possibility, the device comprises a material transparent to scintillation photons, extending between the scintillator detector and at least one planar face.

[0026] The device may comprise a spectrometric detector extending opposite the capillary, and connected to the processing unit. The spectrometric detector is connected to the processing unit, the processing unit being configured to detect the presence of impurities, in particular metallic impurities, in the liquid, from X-ray fluorescence peaks detected on a spectrum generated by the spectrometric detector.

[0027] Preferably, the device comprises a motorized translation unit, configured to move, in translation, the capillary, along the longitudinal axis, so that the capillary can pass between the measurement position, facing the scintillator detector, to at least one sampling position, the sampling position being offset, along the longitudinal axis, relative to the measurement position.

[0028] The device may comprise a pumping unit, configured to:

[0029] - admit, in the sampling position, the liquid into the internal space of the capillary when the capillary is in contact with a solution contained in a reservoir, the liquid contained in the capillary constituting a sample of said solution;

[0030] - and / or push back the liquid from the internal space of the capillary.

[0031] According to one possibility, the capillary comprises an internal face, delimiting the internal space, the internal face being hydrophobic. According to a preferred embodiment,

[0032] - the detection signal resulting from each photodetector comprises pulses, each pulse resulting from an interaction of a particle, forming the ionizing radiation, in the scintillator detector;

[0033] - the processing unit comprises a coincidence detection circuit, configured to detect pulses detected in temporal coincidence by at least two photodetectors;

[0034] - the processing unit is programmed to estimate the activity based on a quantity of pulses detected in temporal coincidence.

[0035] Preferably, the device comprises at least three photodetectors. The coincidence detection circuit is programmed to allow detection of pulses detected in temporal coincidences by two detectors, called double coincidences, and detection of pulses detected in temporal coincidences by three detectors, called triple coincidences. The processing unit can be programmed to estimate the activity as a function of a number of double coincidences detected per unit of time. The activity can be estimated from a detection efficiency, obtained by comparing a quantity of double coincidences with a quantity of triple coincidences detected over the same measurement period.The device may comprise an observation camera, arranged to view the capillary when the capillary occupies an observation position, offset from the measurement position, the processing unit being programmed to estimate a volume of liquid in the capillary based on an image provided by the observation camera.

[0036] A second subject of the invention is a method for estimating an activity of a liquid using a device according to the first subject of the invention, comprising the following steps a) introduction of a liquid sample into the capillary; b) arrangement of the capillary in the measurement position; c) acquisition of detection signals by each photodetector; d) as a function of the acquired detection signals, estimation of the activity of the liquid sample, present in the capillary, using the processing unit.

[0037] According to one possibility,

[0038] - during step a), the capillary occupies a sampling position, in contact with a reservoir containing the liquid;

[0039] - between step a) and step b), the capillary is moved by the translation unit, from the sampling position to the measuring position. According to one possibility,

[0040] - the device comprises a pumping unit, as previously described;

[0041] - during step a), the pumping unit is activated, so as to suck part of the liquid, present in the reservoir, towards the capillary.

[0042] Step d) may include:

[0043] - detection, in the detection signals, of pulses emitted in temporal coincidence, by two photodetectors, called double coincidences;

[0044] - taking into account a detection efficiency relative to double coincidences;

[0045] - determination of activity from a number of double coincidences detected per unit of time and the detection efficiency relative to double coincidences.

[0046] According to one possibility,

[0047] - the device has three photodetectors

[0048] - the detection efficiency relative to double coincidences is calculated from a ratio between

[0049] • a number of pulses emitted, in the detection signals, in temporal coincidence, by three photodetectors, called triple coincidences;

[0050] • the number of double coincidences.

[0051] Another object of the invention is a scintillator detector, crossed by a cylindrical opening, the cylindrical opening extending along a central axis, the scintillator detector comprising:

[0052] - a central portion, formed of a solid material configured to generate scintillation photons under the effect of exposure to ionizing radiation, the central portion extending around the opening;

[0053] - planar faces, optically coupled to the central portion, each planar face being configured to be coupled to a photodetector.

[0054] According to one possibility, the central portion is spherical, and extends around the cylindrical opening. According to another possibility, the central portion is cylindrical, and extends around the opening, around an axis coaxial with the central axis. According to another possibility, the central portion is polyhedral, for example cubic.

[0055] Preferably, the central portion has rotational symmetry about the central axis.

[0056] Preferably, the central portion extends, from the central axis, along a radius greater than

[0057] 5 mm or 10 mm. The invention will be better understood by reading the description of the exemplary embodiments presented in the remainder of the description, in conjunction with the figures listed below.

[0058] FIGURES

[0059] Figures 1A to 1C represent an example of a device according to the invention. In Figures 1A, 1B and 1C, a capillary of the device is respectively arranged in a sampling position, an observation position and a measurement position.

[0060] Figure 1D shows a shutter and bellows intended to seal the measurement module against ambient light.

[0061] Figure 2A shows an example of a scintillator detector.

[0062] Figure 2B shows the scintillator detector, described in connection with Figure 2A, coupled to three photomultipliers.

[0063] Figure 2C shows another example of a scintillator detector.

[0064] Figure 2D schematically shows another example of a scintillator detector.

[0065] Figures 3A and 3B show other possible configurations of the scintillator detector.

[0066] Figures 4A and 4B represent a modeled scintillator detector geometry, in two different section planes.

[0067] Figures 5A and 5B are detection spectra, representing a probability of energy deposition by particles emitted by an activity of lBq of 18 F and n C.

[0068] Figure 6A shows an image of the sample, placed in the observation position.

[0069] Figure 6B shows an image of a graduated optical calibration object.

[0070] Figure 6C represents a processing of the image shown in Figure 6B.

[0071] Figure 6D shows an image of another sample, placed in the observation position.

[0072] Figure 7 shows schematically the main steps of a method implementing the device according to the invention.

[0073] PRESENTATION OF SPECIAL EMBODIMENTS

[0074] Figures 1A to 1C represent an embodiment of a device 1 according to the invention. The objective of the device is to quantify an activity of a small volume, typically a few pL, of a radiopharmaceutical solution comprising a radioactive isotope. The radioactive isotope is known. It may in particular be an isotope as described in the prior art.

[0075] Generally, the volume or mass activity of a solution intended to be injected into a patient's body is very high. In order to obtain an activity measurement with good precision, it is preferable to use a small sample volume, so as to avoid saturation of the detector used. The inventors consider that a volume of less than 10 pL, and preferably 1 pL or a few pL, is optimal. The volume can also be of the order of a few 100 nL or a few 10 nL or even of the order of nL. The volume activity is high enough for the total activity to be easily measured. Furthermore, the fact that the total activity of the sample is high enough makes it possible to carry out measurements spaced out over time, and to verify that the decrease in activity as a function of time is consistent with the radioactive half-life of the isotope.

[0076] The radiopharmaceutical solution to be injected is contained, in liquid form, in a reservoir 20. An important element of the invention is the use of a capillary 3, intended to collect the sample 2 of the pharmaceutical solution. In the example shown, the capillary 3 is a quartz (fused silica) capillary, 15 cm long, with an internal diameter of 900 μm and an external diameter of 1200 μm. The capillary 3 extends around a longitudinal axis A. In this example, the longitudinal axis A is parallel to a vertical axis Z. The horizontal plane P X Y is defined by two orthogonal axes X and Y.

[0077] The capillary 3 is movable in translation using a translation plate 4, preferably motorized. In the example shown, the translation plate is configured to move along a mast 5, parallel to the longitudinal axis A. The translation plate allows translation, along the longitudinal axis A, of the capillary. The capillary can thus occupy different positions along the longitudinal axis, as described below.

[0078] The device 1 comprises a measurement module 10, intended to quantify the activity of the sample 2 previously taken from the capillary 3. The translation plate 4 is thus configured to move the capillary between: a sampling position, in contact with the container 20, so as to take a sample 2 of radiopharmaceutical solution: the sampling position is shown in Figure 1A. The sample 2 is thus formed by a drop, or by several drops, resulting from the sampling. an observation position, during which the sample 2 is placed facing an observation camera 30: the sampling position is shown in Figure 1B. a measurement position, during which the sample 2 is placed in the measurement module 10: the sampling position is shown in Figure 1C.

[0079] The device is arranged so that when the capillary occupies the sampling position, the capillary is engaged in the reservoir 20, so as to be in contact with the radiopharmaceutical solution. The reservoir 20 is removable and may not be part of the device. It may be a simple bottle. The capillary 3 is connected, by a fluid connection, to a pumping unit 21. In this example, the capillary plunges into the reservoir 20 by a first end 3i. The capillary has a second end 32 opposite the first end 31. The second end 32 is connected, by a steel tube 22, to the pumping unit 21. In this example, the pumping unit 21 is a syringe connected to a syringe pump. The steel tube 22 (internal diameter 2 mm), acts as a fluid connection between the capillary 3 and the pumping unit 21.Under the effect of the actuation of the syringe pump, the pumping unit allows the application of a depression or an overpressure in the capillary. This allows pumping or delivery of the radiopharmaceutical solution through the first end 3i of the capillary. A liquid sample 2 is thus taken. The admission of the liquid sample 2 into the capillary 3 has been represented in Figure 1A by an arrow.

[0080] The device may comprise a tracking camera 23, configured to visualize the admission of the liquid sample into the capillary 3. The tracking camera 23 is arranged to allow visualization of the position of the capillary 3 relative to the solution present in the reservoir 20. When the first end 3i immerses in the solution, the pumping unit 21 can be actuated. The device 1 may comprise a scale 24, supporting the reservoir 20.

[0081] Following the collection of sample 2, the capillary 3 is translated by the translation unit 4, so as to move away from the reservoir 20. The pumping unit 21 can be actuated, so as to move the sample 2 inside the capillary 3.

[0082] The capillary 3 is then moved, parallel to the longitudinal axis A, to an observation position, facing an observation camera 30. The observation camera makes it possible to form an image of the capillary 3, so as to estimate the volume of the sample 2. The calculation of the volume of the sample is described subsequently, in connection with FIGS. 6A to 6D. A light source 31 is arranged so that when the capillary occupies the observation position, the sample 2 taken extends between the observation camera 30 and the light source 31. It is understood that for a usable image of the sample to be obtained, the capillary is transparent.

[0083] Following the acquisition of the image of the sample 2 by the observation camera 30, the capillary 3 is translated, by the translation stage 4, to a measurement position. In the measurement position, the sample 2 is placed in the measurement module 10. The device comprises a processing unit 40, connected to the measurement module 10, programmed to estimate an activity of the sample 2 from detection signals from the measurement module 10. Thus, unlike the prior art, the capillary delimits an internal space, which comprises the sample 2 whose activity is measured. The capillary thus forms a measurement chamber.

[0084] The measurement module 10 includes the instrumentation allowing an estimation of the activity of the sample. The implementation of the measurement module assumes that the radioactive isotope contained in the sample is known.

[0085] Figures 2A and 2B schematically represent a scintillator detector 11 whose layout is particularly suitable for the intended application. Figure 2A is a three-dimensional view, while Figure 2B is a sectional view, in a plane perpendicular to the central axis, passing through the center of the scintillator detector. The scintillator detector 11 is formed from a solid material configured to generate scintillation photons when exposed to particles forming ionizing radiation. These may in particular be charged particles, such as P" or +, or X or y photons. The scintillation material can be an organic polymer, to which fluorescent dopants have been added. It can also be an inorganic scintillator, for example YaG(Ce), NaI, CsI, LaBrs, BGO (Bismuth Germanate). The use of an inorganic scintillator increases the sensitivity of the measurement because the stopping power of this type of scintillator is higher than the stopping power of organic scintillators. In addition, inorganic scintillators contain atoms with a higher atomic number than organic compounds. This promotes photoelectric interactions, during which the photons release all their energy in the scintillator material in a single interaction.

[0086] Despite their lower sensitivity compared to inorganic scintillators, an important advantage of organic scintillator materials is their ease of shaping, which can be achieved by molding. Figures 2A to 2D show different configurations of an organic scintillator detector, based on vinyl-toluene, which can be obtained by molding.

[0087] The scintillator detector 11 is optically coupled to several photodetectors 15. These may in particular be photomultipliers, for example of the Hamamatsu H13175U-110 type. Preferably, the scintillator detector 11 comprises or is optically coupled to planar faces 12, each photodetector 15 being applied against a planar face 12, possibly using a coupling fluid. According to one possibility, at least one photodetector, or even each photodetector, is or comprises a photodiode. It may for example be a photodetector of the SiPM (Si photomultiplier) type. An important aspect of the scintillator detector is that it is crossed by an opening 13, extending around a central axis A'. When using the scintillator detector in the device 1, the central axis A' coincides with the longitudinal axis A.The opening 13 is sized to allow translation of the capillary 3 through the scintillator detector 11. For example, when the external diameter of the capillary 3 is 1.2 mm, the diameter of the opening 13 may be equal to 1.4 mm. Generally, the diameter of the opening is preferably between 1 mm and 1 cm.

[0088] The scintillator detector can have a parallelepiped shape, with four flat faces parallel to the central axis A'. Such a possibility is shown schematically in Figure 3A. It can also have a polyhedral shape, with flat faces parallel to the central axis A'

[0089] Preferably, the scintillator detector has rotational symmetry about the central axis A'. In the example shown in Figures 2A and 2B, the scintillator detector has a central portion 11', of spherical shape, extending around the opening 13. The spherical portion 11' is arranged around the opening 13, and preferably symmetrically around the central axis A'. The fact that the scintillator material has a spherical portion, around the opening 13, is considered advantageous for reasons of symmetry, in particular during the processing of detection signals described below.

[0090] According to one possibility, the scintillator detector 11 may comprise a cylindrical central portion, extending around the central axis A'. Such a possibility is shown in FIG. 3B. The wall of the capillary may be formed of a scintillator material.

[0091] When the central portion 11' is a sphere or a cylinder, its radius can be between 15 mm and 25 mm when the scintillator material is an organic scintillator. The radius is for example equal to 18 mm. The optimal dimensions vary depending on the type of scintillator material used. It is considered optimal for the central portion 11' to be spherical.

[0092] In order to facilitate coupling with the photodetectors 15, the scintillator detector 11 comprises planar faces 12, and preferably parallel to the central axis A'. In Figures 2A and 2B, the scintillator is a single piece. It comprises cylindrical coupling portions 14, each coupling portion 14 extending between the central portion 11' and a planar face 12. Each planar face 12 extends perpendicular to a detection axis, which is intersecting, and preferably perpendicular, to the central axis A'. In Figure 2B, three different detection axes 6i, 62 and 63 are shown, perpendicular to which three different planar faces 12 extend. Preferably, the detection axes are distributed according to a symmetry around the central axis A'. Preferably, the detection axes are coplanar. The plane along which the detection axes extend is preferably perpendicular to the central axis A'.In the example of Figure 2B, the adjacent detection axes are angularly offset by the same angle θ equal to 120°. According to other possibilities, the scintillator comprises two planar faces, perpendicular to a detection axis, which corresponds to an angular offset of 180°. According to another possibility, the scintillator comprises four planar faces, such that the detection axes of two adjacent planar faces are angularly offset by 90°. More generally, the scintillator 11 may comprise n planar faces 12, arranged so that the respective detection axes of two adjacent planar faces are offset by an angle θ equal to 360° / n.

[0093] In the example of Figures 2A and 2B, the scintillator 11 is a single piece: the central portion 11' and each coupling portion 14 are formed from the same scintillator material. Such a configuration can be obtained by molding when the scintillator material is organic. In the example of Figure 2C, the central portion 11' is formed from a scintillator material, while each coupling portion 14 is formed from a material transparent to scintillation photons. Each coupling portion 14 is attached to the central portion 11'. Figure 2C is a view in a section plane passing through each detection axis.

[0094] Figure 2D is also a view in a section plane passing through each detection axis. In Figure 2D, the central portion 11' is truncated, so as to form the planar faces 12. In this configuration, there is no coupling portion 14.

[0095] The measurement module 10 may comprise a spectrometric detector 17. In Figure 2B, a spectrometric detector 17 is shown, arranged opposite the scintillator detector 11. The spectrometric detector is configured to detect X or gamma photons emanating from the scintillator 11. It is connected to a spectrometry circuit 17', configured to form an energy spectrum. More precisely, during each detection of a photon by the spectrometric detector, the latter generates a pulse whose amplitude is correlated to the energy deposited by the photon in the spectrometric detector. The spectrometry circuit 17' allows a spectrum to be formed, which corresponds to a histogram of the amplitudes of the pulses resulting from the spectrometric detector 17. The spectrum corresponds to a number of pulses detected, during an acquisition period, for different energy channels. The spectrometry circuit is connected to the processing unit 40.More precisely, the processing unit implements a spectral analysis algorithm, allowing the identification of certain singularities. These may be radioactive impurities. They may also be peaks resulting from the X-ray fluorescence of certain materials, in particular metallic materials, for example Fe, In or Pd. Metallic materials, resulting from the production process of the radioactive isotope, form impurities in the radiopharmaceutical solution. The excitation, inducing X-ray fluorescence, may come from X-rays or gamma rays emitted directly or indirectly by the isotope. For example, when the isotope is a p-emitting. + , fluorescence can be induced by irradiation of the sample with photons resulting from the annihilation of the p particle + .

[0096] The spectrometric detector may use a detection material of the CeBra or Nal(TI) type or or Csl or CdTe type. This type of material makes it possible to form a spectrum of acceptable quality using a spectrometric detector that is compact enough to be integrated into the detection module 10. The spectrometric detector may be of the GeHP type, provided that an adequate cooling means is available, for example a cryogenic tank or thermoelectric cooling.

[0097] The detection module 10 extends, along the longitudinal axis A, between a lower face 10i n r and an upper face 10 sup . Given the presence of the photodetectors 15, which can be sensitive to visible light, the detection module 10 is made watertight by using a shutter 18, on the lower face 10i n r facing the container 20, and by an opaque bellows 19, extending around the capillary, from the upper face 10sup . Figure 1D shows schematically the arrangement of the shutter 18 and the bellows 19 on the detection module. When the capillary 3 is in the measuring position, the shutter is closed. The opening of the shutter allows a translation of the capillary so that the sample 2 is outside the measuring module, for example in the observation position or in the sampling position. The opaque bellows is configured to fold or refold depending on the translation of the capillary 3.

[0098] The inventors established a numerical model in order to simulate the detection performance of a scintillator detector as described in connection with Figures 2A and 2B. Figure 4A shows a sectional view of the numerical model, in an XZ plane, passing through the central axis. Figure 4B shows a sectional view of the numerical model, in an XY plane, perpendicular to the central axis, and passing through the center of the spherical portion 11'. Such a numerical model is intended to estimate the energy absorbed by the scintillator detector when the latter is subjected to exposure to radiation produced by a predetermined isotope. In Figure 5A, there is shown, for a disintegration of + of 18F, a probability density of releasing, in the scintillator detector, different energy values. The abscissa axis corresponds to the energy, expressed in keV. The ordinate axis represents, at each disintegration, a probability of depositing, in the scintillator detector, the energy corresponding to the abscissa axis. In Figure 5A, curve a) corresponds to the energy deposited by a positron emitted by 18 F, without taking into account annihilation. Curve b) corresponds to the energy deposited by the two gamma photons of energy 511 keV resulting from the annihilation of the positron. Curve c) corresponds to an energy deposition probability combining the path of the positron in the scintillator detector as well as the annihilation, giving rise to the emission of 511 keV photons. Curve d) corresponds to curve c) taking into account a branching factor of 97% of the decay + For 18 F.

[0099] Figure 5B is a figure similar to Figure 5A, established by considering the disintegration + of 11C, the branching rate being 99%.

[0100] In Figures 5A and 5B, the low energy emissions due to electron capture do not pass through sample 2 or capillary 3. They do not release any energy in scintillator detector 11.

[0101] In Figures 5A and 5B, the sample is a drop of physiological liquid with a unit activity of 1 Bq respectively 18 F and of n C.

[0102] Curves d) of Figures 5A and 5B correspond to absorption spectra of the scintillator detector, respectively for an activity of 1Bq of 18 F and n C. These absorption spectra can be used as input data for the determination of the activity of a sample 2, as described later.

[0103] When implementing the device 1, the processing unit 40 is connected to each photodetector 15, and collects a detection signal generated by each of them. More precisely, each photodetector is connected to a coincidence detection circuit 16, intended to determine the pulses detected in temporal coincidence by two photodetectors (double coincidences) as well as by the three photodetectors (triple coincidences). As described in the publication Broda R. et al “Radionuclide metrology using liquid scintillation counting”, Metrologia 44 (2007), when using a sample, considered as a pure P emitter, of unknown activity, it can be shown that a detection efficiency q, called absolute detection efficiency, can be determined from a ratio between the number of triple coincidences to the number of double coincidences.

[0104] More precisely, if N T corresponds to the number of triple coincidences and N Dcorresponds to the number of double coincidences, the ratio — , designated RCTD (Ratio of triple coincidences on

[0105] ND doubles), is such that: Or :

[0106] S(E) is the absorption spectrum of the isotope considered, which corresponds to curves d) of figures 5A (for 18 F) and figures 5B (for U C); v is the quantum efficiency of the photomultipliers, which is not known; r] Q is a light output of the scintillator material, which corresponds to a number of scintillation photons emitted per unit of absorbed energy (photons. keV 1 ) ; of

[0107] — is the linear energy loss of an incident particle (B + or B) in the scintillator dx detector;

[0108] E max is the maximum energy of the emission spectrum of the incident particle; kB is a semi-empirical parameter, usually called the Birks parameter, expressed in cm. MeV1 This parameter describes the nonlinearity of the scintillator. It is usually between 0.007 and 0.015 cm. MeV 1 . of

[0109] The parameters S(E),— , and kB are input data. RCTD is a measured data, resulting from the coincidence detection circuit 16. We can determine the product vr] Q , product of the quantum efficiency of the photomultipliers by the luminous efficiency of the scintillator material, so as to obtain the absolute detection efficiency rj. The efficiency r] calculated is that which allows us to verify equality (1).

[0110] The calculated efficiency r] is used to determine a detection efficiency E D double coincidences, according to the expression: s D = (3(1 — e -î? ) 2 — 2(1 — e -î? ) 2 ) (3)

[0111] The activity Act of the isotope is then determined, from ÏVp, with:

[0112] N Dcorresponds to a so-called logical sum of the double coincidences detected per unit of time. For example, if we have three photodetectors 15i, 152 and 153, N D is such that:

[0113] IV D — N 1 2 + ^1.3 + ^2.3 N 1 2 ,3 ( ) where N 1 2 , N 13 and N 2 3 are the number of double coincidences detected, per unit of time, by the photodetectors 15i and 152, 15i and 153, 152 and 153 respectively. ÏV 1 2 ,3 corresponds to the number of triple coincidences detected per unit of time: ÏV 1 2 ,3 = T (6). The processing unit 40 receives the quantities N 12 , ^1,3 and / V2,s and N T of the coincidence circuit 16. It can then determine r] by implementing expression (1). This allows us to obtain e D by implementing (3), from r], then the activity Act by the expression (4).

[0114] Preferably, the efficiency r] is determined during each measurement, by a ratio between the number of triple coincidences on the number of double coincidences. The efficiency of detection of double coincidences s D can thus be determined, according to (3), during each measurement. This avoids the need for calibration carried out in the laboratory, which is a notable advantage of the invention.

[0115] The activity Act of sample 2 can be estimated at different successive measurement times t, in order to obtain ct(t) values. The evolution of ct(t) as a function of time can be compared with a theoretical evolution, established from the decay period of the isotope considered. A difference between the measured evolution and the theoretical evolution can mean the presence of pollution in sample 2.

[0116] The activity ct(t) of sample 2, measured at the measurement time t, is preferably normalized by the volume of the sample. This allows an estimation of the volume or mass activity of the radiopharmaceutical solution present in the container 20.

[0117] The volume of the sample can be estimated using an image acquired by the observation camera 30, while the sample 2 occupies the observation position. Given the geometry of the capillary, without any particular treatment, the sample extends between two menisci, as shown in FIG. 6A. The processing unit 40 receives the image acquired by the observation camera, and can estimate a volume V of the sample, for example by applying the expression: Or :

[0118] - L is the total length of the sample;

[0119] - r is the internal radius of the capillary;

[0120] - is a height of the first meniscus;

[0121] - H2 is a height of the second meniscus.

[0122] The quantities L, r, and H2are estimated from the image. The observation camera has previously been calibrated, for example by acquiring an image of a target or a graduated ruler. Figure 6B shows an image from an Olympus OB-M object micrometer. Figure 6C shows an intensity profile of an acquired image, with each peak corresponding to a graduation. In Figure 6C, the y-axis corresponds to an intensity and the x-axis corresponds to pixels aligned along the light line shown in Figure 6B. Since the distance between each graduation is known, a dimension seen by each pixel of the observation camera can be estimated. It is estimated that the performance of the observation camera allows a volume of 1 pL to be estimated with an uncertainty of less than 1%.

[0123] According to one possibility, the inner wall of the capillary is hydrophobic, or has been subjected to a hydrophobic treatment. Such a treatment makes it possible to reduce, or even eliminate, the presence of menisci on either side of the sample. Figure 6D is an image of a sample 2 in a capillary whose inner face has previously been subjected to a hydrophobic treatment. It is understood that the estimation of the volume of the sample, from the observation image, is simpler, because the geometry of the sample corresponds to a cylinder.

[0124] After the activity of the sample has been determined, the capillary is translated to the sampling position and the sample can be forced back into the reservoir 20 by applying an overpressure in the capillary.

[0125] Alternatively, capillary 3 may be directly made from an inorganic scintillator material that exhibits mechanical and surface finish characteristics similar to glass or quartz.

[0126] The same surface treatment as for glass can be applied to make it hydrophobic and prevent surface contamination.

[0127] Such a capillary allows both liquid sampling, image capture for volume measurement and detection of the radiation emitted by the liquid. Any non-hygroscopic inorganic scintillator can be used such as YAG(Ce) (Yttrium Aluminum Garnet doped with Cerium), YAP(Ce) (Yttrium Aluminum Perovskite doped with Cerium), GaGG(Ce) (Gadolinium Aluminum Garnet doped with Cerium)....

[0128] As in the previously described embodiments, the capillary can be inserted into the scintillator detector 11.

[0129] The scintillator detector 11, into which the capillary 3 is inserted, is preferably of the same composition as that of the capillary.

[0130] Figure 7 shows the main steps of a method for implementing a device as previously described.

[0131] During a step 100, the capillary is moved into the sampling position and a sample 2 is taken under the effect of the pumping unit.

[0132] During a step 110, the capillary is placed in the observation position and an image of the sample is acquired by the observation camera, which makes it possible to estimate the volume (or mass) of the sample.

[0133] During a step 120, the capillary is placed in the measurement position, in the measurement module 10. The activity of the sample is estimated from the detection signals resulting from each photodetector, and from the number of double coincidence detections detected. Step 120 can be implemented before step 110.

[0134] The inventors used a device as previously described, the scintillator detector being like that described in connection with Figures 2A and 2B. After each measurement, each sample was ejected into a liquid scintillation solution, so as to obtain a reference measurement. The isotope was 18 Mad n C. Table 1 summarizes the experimental results obtained.

[0135] Table 1 In Table 1, the third and fourth columns correspond respectively to the volume activity determined by implementing the invention and the reference method. In Test 1, a capillary was used without hydrophobic treatment. In Test 1, the capillary had been subjected to a hydrophobic treatment, which may explain the smaller difference between the implementation of the invention and the reference method.

[0136] The device which is the subject of the invention makes it possible to estimate the activity of a radioactive liquid without requiring complex calibration, involving a reference laboratory. Indeed, the measurement is carried out on a small volume sample, taken from a radiopharmaceutical solution. The activity is estimated on the basis of double coincidence measurements, as previously described, the detection efficiency being able to be calculated by a ratio of triple coincidences to double coincidences.

[0137] The device of the invention is easily automated, which limits the need for operators to intervene near the radioactive liquid. Indeed, the translation of the capillary, the control of the pumping unit and that of the measuring module can be automated. This helps to reduce the dosimetry of the personnel involved.

Claims

DEMANDS 1. Device (1) for measuring the activity of a radioactive liquid (2), comprising: - a detection module (10), extending around a measuring chamber (3), intended to contain the liquid, the detection module being configured to detect ionizing radiation emitted in the measuring chamber and to emit a detection signal dependent on a quantity of radiation detected; - a processing unit (40), connected to the detection module, and programmed to estimate the activity of the radioactive liquid from the detection signal; the device being characterized in that - The detection module includes: • a solid scintillator detector (11), configured to produce scintillation photons when exposed to ionizing radiation, the scintillator detector extending around the measurement chamber; • at least two photodetectors (15), optically coupled to the scintillator detector, each photodetector being configured to detect scintillation photons and generate a detection signal dependent on the quantity of scintillation photons detected; - the device includes a capillary (3), extending around a longitudinal axis (A), and delimiting an internal space intended to contain the radioactive liquid, the capillary being arranged to be positioned in a measurement position, in which the scintillator detector extends around the internal space of the capillary, the capillary forming the measurement chamber.

2. Device according to claim 1, wherein the scintillator detector extends around the capillary.

3. Device according to any one of the preceding claims, wherein the scintillator detector forms a wall of the capillary.

4. A device according to any one of the preceding claims, wherein: - an opening (13) is made through the scintillator detector (11) along the longitudinal axis (A); the capillary extends through the opening when it is positioned for measurement.

5. Device according to any one of the preceding claims, in which each photodetector extends around a detection axis (6i, 62, 63), secant from the longitudinal axis.

6. Device according to claim 5, wherein the respective detection axes of each photodetector are coplanar.

7. Device according to any one of claims 5 or 6 in which the respective detection axes (61, 62, 63) of each photodetector (15) are regularly spaced angularly from each other, around the longitudinal axis.

8. Device according to any one of claims 4 to 7, in which the scintillator detector (11) comprises a central spherical or cylindrical or polyhedral portion (11'), through which the aperture (13) passes.

9. Device according to any one of the preceding claims, wherein each photodetector (15) is optically coupled to the scintillator detector (11) by a flat face (12).

10. Device according to claim 9 and claim 8, wherein the scintillator detector extends, from the opening, to at least one flat face (12), so that the scintillator detector comprises the central portion (11'), around the opening, and at least one flat face.

11. Device according to claim 10, in which the scintillator detector (11) has as many flat faces (12) as there are photodetectors.

12. Device according to claim 9, comprising a material transparent to scintillation photons, extending between the scintillator detector and at least one flat face.

13. Device according to any one of the preceding claims, comprising a spectrometric detector (17), extending opposite the capillary, and connected to the processing unit (40), the processing unit being configured to detect the presence of impurities in the liquid from X-ray fluorescence peaks in a spectrum generated by the spectrometric detector.

4. A device according to any one of the preceding claims, comprising a motorized translation unit (4) configured to move the capillary in translation along the longitudinal axis, such that the capillary can pass from the measurement position, facing the scintillator detector, to at least one sampling position, the sampling position being offset, along the longitudinal axis, relative to the measurement position.

5. A device according to claim 14, comprising a pumping unit (21) configured to: - admit, in the sampling position, the liquid into the internal space of the capillary when the capillary is in contact with a solution contained in a reservoir, the liquid contained in the capillary constituting a sample of said solution; - and / or expel the fluid from the internal space of the capillary.

6. A device according to any one of the preceding claims, wherein the capillary comprises an inner face delimiting the internal space, the inner face being hydrophobic.

7. A device according to any one of the preceding claims, wherein - the detection signal resulting from each photodetector consists of pulses, each pulse resulting from an interaction of a particle, forming the ionizing radiation, in the scintillator detector; - the processing unit includes a coincidence detection circuit (16), configured to detect pulses detected in temporal coincidence by at least two photodetectors; - the processing unit (40) is programmed to estimate the activity based on a quantity of pulses detected in temporal coincidence.

8. Device according to any one of the preceding claims, comprising an observation camera (30), arranged to view the capillary when the capillary occupies an observation position, offset from the measurement position, the processing unit being programmed to estimate a volume of liquid in the capillary based on an image provided by the observation camera.

9. Method for estimating the activity of a liquid using a device according to any one of the preceding claims, comprising the following steps: a) introduction of a liquid sample (2) into the capillary (3); b) arrangement of the capillary in the measurement position; c) acquisition of detection signals by each photodetector (15); d) as a function of the acquired detection signals, estimation of the activity of the liquid sample, present in the capillary, using the processing unit.

20. A method according to claim 19, wherein the device is a device according to claim 14, and wherein: - during step a), the capillary occupies a sampling position, in contact with a reservoir containing the liquid; - between step a) and step b), the capillary is moved by the translation unit from the sampling position to the measurement position.

21. A method according to claim 20, wherein - the device is a device according to claim 15; - during step a), the pumping unit is activated, so as to draw some of the liquid, present in the reservoir, towards the capillary.

22. A method according to any one of claims 19 to 21, wherein step d) comprises: - detection, in the detection signals, of pulses emitted in temporal coincidence, by two photodetectors, called double coincidences; - consideration of a detection yield relative to double coincidences (£ D ); - determination of activity from a number of double coincidences detected per unit of time and the detection yield relative to double coincidences.

23. A method according to claim 22, wherein - The device includes three photodetectors - the detection yield for double coincidences is calculated from a ratio between • a number of pulses emitted, in the detection signals, in temporal coincidence, by three photodetectors, called triple coincidences; the number of double coincidences.

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