CN107544086A - Gamma photon detecting and imaging device and method - Google Patents
Gamma photon detecting and imaging device and method Download PDFInfo
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Abstract
The invention provides a gamma photon detection device and a gamma photon detection method. The method comprises the steps of utilizing the plurality of detection probes to detect horse adding photons generated by a target object, enabling the horse adding photons to firstly act with a first layer of detector and then act with a second layer of detector, then obtaining an electric signal generated by each detection probe in at least one first time period, and respectively carrying out first time signal coincidence calculation on the electric signals generated by the plurality of scintillation crystal detectors of each detection probe so as to obtain a plurality of first time signal related data. Finally, the electrical signal generated by the first layer scintillation crystal detector of each detection probe in at least one second time period is obtained, and a second time signal coincidence calculation is carried out to obtain a plurality of pairs of second time signal related data. And performing activity distribution reconstruction by using the first and second time signal related data.
Description
Technical field
The present invention is a kind of plus horse photon detection apparatus and method, particularly relates to a kind of detecting wink Fa Jiama photon
(prompt gamma ray) and positron mutually ruin plus horse (positron annihilation gamma ray) plus horse photon
Detect imaging device and method.
Background technology
As shown in figure 1, radiotherapy (Radiotherapy, RT) is exactly the photon (such as x-ray) or band with high-energy
Charged particle is come at irradiated lesion, one kind side for the treatment of for the purpose of reaching " kill malignant tumour " or " suppressing malignant tumour hyperplasia "
Formula.Wherein, curve 90 represents X-ray dosage and tissue depth relation, due to x-ray and the physical characteristic of material effect, with penetrating
Line enters the increase of tissue depth, and relative dosage is also gradually decayed with depth, therefore single X-ray beam enters on internal path
There is more dosage to discharge the normal structure before and after tumour, cause x-ray not yet to destroy before tumor carcinoma cells just shadow
Normal structure is rung, or even the normal tissue regions allowed after tumour also have dosage deposition.The mode treated relative to X-ray, curve 91
It is then charged particle, for example, proton or heavy ion, dosage and depth relationship, because material is acted on because of the faster traveling of proton velocity
The energy of unit distance loss is fewer, so the kinetic energy initially discharged into sufferer body surface is at a fairly low, until certain range is deep
Degree, proton or heavy ion kinetic energy produce maximum dose deposition, referred to herein as bragg peak 910 (Bragg Peak) after declining to a great extent,
Almost complete absence of dosage after bragg peak.
Because proton or heavy particle therapy have the characteristic that dosage concentrates on bragg peak, therefore proton or heavy ion range
It is uncertain influence it is more sensitive far beyond X-ray.If proton or heavy ion range prediction have uncertainty, its dose height collection
In bragg peak where depth be expected it is variant, high dose area will be caused to be not covered by whole tumour or high dose area covering
Vitals equivalent risk around to tumour.Therefore proton or heavy particle therapy have to precisely confirm matter in clinical practice
Son or heavy ion range region, are limited in tumor region by its bragg peak and can be only achieved optimal therapeutic effect.
Right proton or heavy particle therapy process still have some factors to influence its inaccuracy, are described as follows：
(1) uncertainty caused by treatment plan：This is due to current treatment plan essentially from X-ray CT images
Hounsfield unit (HU) are tissue and the corresponding relation of electron density, and right proton or heavy ion are acted on biological tissue and led
Consider to be the atomic nucleus of tissue and its stop ability (stopping power), therefore the HU information conversion of CT images is made a living
The stop ability of thing tissue, there will be it uncertain.In addition, CT images artifact, X-ray beam hardening (beam
Hardening) phenomenon etc. is also the uncertain source of existing assessment proton or heavy ion range；
(2) actual therapeutic position and treatment plan are variant：Caused essentially from sufferer Set-up errors, breathing or heartbeat etc.
Treatment target movement etc.；
(3) tumor size of therapeutic process changes, sufferer build changes etc.；And
(4) error caused by the facility for producing proton or heavy ion beam, such as degrader (energy are come from
Degrader), beam forms (beam delivery) relevant apparatus equal error.
Due to above-mentioned range inaccuracy, generally in the clinical target volume (clinical to be treated during clinical treatment
Target volume, CTV) treatment safety scope (safety margin) is increased outside.It is increased because of range uncertainty to control
Scope is treated, increases (30cm advanced tumors can increase about 14mm treatment safeties scope) with tumor depth y.Increase 1cm peaces outside CTV
Gamut then has~80cm3 normal healthy tissues receive with tumour identical dose of radiation, thus increase normal structure nearby
It is impaired to injure carcinogenic risk.If CTV nearby there are the relatively low vitals of radiation tolerance level, will also giving for therapeutic dose be influenceed
And the control rate of malignant tumour.In order to reduce the inaccuracy of therapeutic process, proton or heavy particle therapy Reliability are lifted, such as
Fruit can be monitored in the proton to patient or heavy ions area over the course for the treatment of, confirm road of the proton beam in patient
Whether footpath, which needs, is corrected, and this will can reduce the amplification for the treatment of safety scope, is improved dosage and is given, so lifted tumor control rate with
Therapeutic effect.Therefore how to confirm the path with monitoring proton or HIB in patient is that very important research is discussed
Topic.
In the prior art, there are several developing checking proton range technologies, meeting real-time and Noninvasive technology has
Proton penetrates (proton transmission) radiography, wink Fa Jiama photon radiography and PET (positron emission
Tomography) radiography.Proton penetrates radiography and need to take the extra protons equipment time and can produce additional radiation dosage, also has more
The problems such as Coulomb scattering (multiple Coulomb scattering) effect, is to be overcome, is applied to the machine of clinic in short term
Can be not high.Wink Fa Jiama photon (PG) radiography and PET radiographies be using offspring caused by proton and sufferer function of organization-
Positron emission core and wink Fa Jiama photon do detecting radiography.Positron, which is mutually ruined, adds horse photon and wink Fa Jiama photon all to penetrate sufferer
Body is detected, and can do the measurement imaging of the Noninvasive proton range of live body (in vivo).
Proton and heavy ion duplicate with biological tissue mechanism of action, hereafter are discussed as representing with proton therapeutic, do not repartition
Proton and heavy ion.During proton irradiation, proton adds horse photon with organizing nuclear inelastic collision to produce, and these add horse photon
Two classes are divided into according to generation mechanism is induced.First, when inelastic collision occurs for proton and tissue atomic nucleus, target nucleus is excited
To state is swashed, wink Fa Jiama photon (prompt gamma) is produced within (ns) time nanosecond.It is another that to be that target nucleus is hit by proton broken
Piece (nuclear fragmentation) and produce positron emission core (positron-emitting nuclei), such as O-15
(half-life period:2.037min), C-11 (half-life period:20.385min), N-13 (half-life period:(the Newhauser such as 9.965min)
and Zhang,2015).Positron (positron) caused by positron emission nuclear decay mutually ruins generation with the electronics in tissue
The positron of 511keV energy mutually ruins plus horse (positron annihilation gammas) photon pair.Wink Fa Jiama photon and just
Sub mutually ruin adds horse photon, and their energy all can penetrate sufferer body and be detected and be imaged, and analysis activity distribution image, can obtain
Path of the proton in human body is obtained, accordingly can be applied to the range checking of proton or heavy particle therapy.
Positron is mutually ruined plus horse photon is detected to general using PET radiographies, is more ripe at present and applied to clinic
Live body proton range verification technique.But biological metabolism (biological washout) effect of the positron emission core in patient
Answer, positron emission core limits throughput, half-life short and the space for the treatment of system and PET images align (co-
Registration) error (caused by movement of the sufferer between therapeutic room and PET angiographic instruments) etc., these limit PET confrontation
Sub- range assesses precision.
As for wink Fa Jiama photon, moved because proton kinetic energy needed for generation wink Fa Jiama photon is relatively produced needed for positron emission core
Can be low, so the position of wink Fa Jiama distribution of photons and the position of proton deposition maximum dose are more consistent, therefore sent out using wink
Add horse imaging activity assess bragg peak the degree of accuracy compared with using PET methods come it is high.In addition, wink Fa Jiama photonic throughput calibration
It is sub mutually to ruin plus horse photon is more 60~80 times, in identical detection geometry situation in this representation theory, wink Fa Jiama photon radiography can be with
There is stronger signal, statistical error is come small compared with PET.Have in the prior art and utilize the common collimater Shi Jiama of nucleon medical domain
Camera (collimator-based gamma camera) technology, the slit collimaters or edge- of version are improved by pin hole
Knife collimaters combine plus horse detection device does wink hair gamma rays detecting radiography.But this technology detection inefficient, because of collimation
Device stops that most of photon and the detecting popped one's head in high-energy wink Fa Jiama photons are limited in one's ability.More importantly because of collimater
In the presence of and produce substantial amounts of neutron one of (proton induce secondary radiation particle), these neutrons detect the signal of probe by disturbing
Detecting, signal to noise ratio (signal-to-noise ratio, S/N) reduction is caused, cause to influence activity image definition and sentence using it
The degree of accuracy of disconnected proton range bragg peak.In addition, because the wink Fa Jiama photon energy that radiotherapy induces is high, so collimater
Design is quite thick and heavy (size is high up to the people of 80cm half), takes therapeutic room's confined space.Above-mentioned factor causes collimater Shi Jiama phases
Machine applies the practicality in proton clinical treatment to be limited.
It is now another to gulp down scattering imaging technique because being applied to high-energy light in the more rare Kang Pu of Medical Imaging
Son detecting imaging, so as to turn into the new selection of research proton or heavy particle therapy with wink Fa Jiama photon radiography.Kang Pu gulps down scattering
Imaging technique mainly adds horse photon detection etc. applied to astronomical cosmic ray, nuclear energy power plant, the sensitive nuclear species of Homeland Security.Mesh
Detection design progress Kang Pu before preceding some protons in the world or the directly use of heavy particle therapy team, which is gulped down, is scattering into picture, such as
Visited using bilateral silicon strip type at U.S. oncotherapy center (Peggy and Charles Stephenson Cancer Center)
Head (double-sided silicon strip detector, DSSD) detection device technology, Han Yang University team of South Korea, which utilize, to be added
Horse electronics vertex of a cone radiography (gamma electron vertex imaging, GEVI) detection technology, team of Kyoto Univ Japan profit
Radiography (electron tracking Compton camera, ETCC) detection technology and Mali of the U.S. are gulped down with electronics trace Kang Pu
Cadmium-zinc-teiluride (CdZnTe, CZT) the detection Kang Pu of blue team of university gulps down camera technique.The detecting of these team is popped one's head in or using trip
From chamber (ionization chamber) technology or use semiconductor detection device technology.Especially its energy of semiconductor detection device
Resolution ratio it is at a relatively high (<1%), it is suitably applied Kang Pu and gulps down and is scattering into picture.But for adding horse photon to high-energy, its detection efficiency
Difference and detection device signal response time length (μ s grades).Signal response time length also elongates the deathly still time (dead of detecting probe
Time) so that the unit interval detection counting efficiency for detecting probe is not evident.This kind of detection device can be used in non-medical applications, because
For even days of long-time data acquisition of non-medical radiography tolerable a few hours, counted with obtaining enough detections, if but real
Impose on medical patient, long-time radiography is infeasible.Then counted to obtain enough detections, with a relatively high matter
Sub- dose irradiation, the counting statistics error of wink Fa Jiama imaging just reaches can be by acceptance level.
According to Univ Maryland-Coll Park USA's Dr.J.C.Polf practical experience, even with above-mentioned highest detection efficiency
CdZnTe detecting probes carry out proton therapeutic wink Fa Jiama radiographies, and its required dosage is still more clinical high more than 100 times.Detectd to make up
Device efficiency deficiency to be examined, also there is the design for using tens of layers of detection device, right detection device is considerable plus electronic system overall dimensions,
This design is less favorable for the limited proton therapeutic room application in space.In addition, because detection device signal response time is up to microsecond
(μ s), so the temporal resolution of scattering detection device and absorption detection device is also in microsecond scale.The temporal resolution of Microsecond grade
Radiography instrument application may cause more than 80% detecting to be counted as the connection that is independent of each other in the Fa Jiama photons monitoring of proton therapeutic wink
It is non-real when news meet event (non-true coincident events), this will cause wink Fa Jiama photon to penetrate source position
Erroneous judgement.It is applied to astronomical, airport customs violated radiation source detecting because past Kang Pu gulps down scattering imaging probe, because universe is penetrated
Line, which reaches the flux finite of the earth and violated radiation source, shielding protection, high intensity ambient interferences is not had, so during Microsecond grade
Between resolution ratio be enough to deal with non-medical demand.In a word, directly application is existing for set by astronomical, territory and nuclear energy demand for security
The wink Fa Jiama photon radiography application that the DSSD types of meter, CZT types are popped one's head in proton therapeutic have that detection efficiency is low, time resolution is poor and
News meet the shortcomings of event rates are too high when non-real, and this will influence system signal to noise ratio, image definition and proton range Prague
Peak estimation accuracy, it is scattering into so penetrating meter Kang Pu for proton therapeutic demand body and gulping down as detecting probe has its necessity.
In addition, prior art such as U.S. Publication patent US6,484, No. 051, the technology discloses one kind and can detectd simultaneously
Positron caused by surveying isotope mutually ruins plus the device of horse photon and wink Fa Jiama photon, due to needing to measure simultaneously, therefore
Three detection devices are at least needed to work simultaneously.In addition, the signal of wink Fa Jiama photon is mutually ruined for positron adds the tens of of horse photon
Times, while if measurement, detecting counting rate (counting rate) will mutually be ruined by the positron of low generation rate (yield rate) to be added
Horse photon numbers are dominated, and then have influence on the signal to noise ratio of detection signal, so as to reduce the quality of image reconstruction.In addition U.S. Publication
Patent US9,069,089 discloses a kind of positron that can detect simultaneously and mutually ruins and the technology of wink Fa Jiama photon, in this skill
In art, the sensor for adding the periphery of horse photon sensor that sensing wink Fa Jiama photon is set mutually is ruined in positron, passes through two kinds of differences
Sensor sense plus horse photon.
The content of the invention
The present invention provides a kind of plus horse photon detection apparatus and method, its using fast blink detection device (such as with LSO,
The scintillation crystals such as LYSO, LaBr3 are material person), scattering detection technology is gulped down with reference to PET and Kang Pu, manufacture has measurement positron mutual
Ruin two-in-one (2-in-1) the detection system of photon pair and wink Fa Jiama photon, recycle sequential keyboard encoder data acquisition carry out radiography and
The embedded Kang Pu of PET gulp down imaging calculation method and carry out image reconstruction and visual fusion.Two-in-one detection system, which has, measures positron
The radiography function of photon pair and wink Fa Jiama photon is mutually ruined, a machine dual purpose, convenience is high, and the difunctional imaging fusions of PET/PG are made
Information obtained by shadow can more improve the quality of image and proton/heavy ion range checking precision.
Provided by the invention plus horse photon detection apparatus and method take shared probe and sequential keyboard encoder data acquisition, and its is excellent
Point apart from a saving of costs, can more lift image signal to noise ratio, and its reason is that the signal of wink Fa Jiama photon is mutual for positron
The decades of times of photon pair is ruined, the present invention adds horse photon pair by individually measuring wink Fa Jiama photon signal and positron and mutually ruining, can
To allow both photons not influence each other, therefore positron can be taken into account and mutually ruined and add horse photon and wink Fa Jiama photon for rebuilding
Activity is distributed the advantages of image.
Provided by the invention plus horse photon detection apparatus and method, can be when proton/heavy particle radiotherapy or nucleon doctor
Dual-isotope (mixing positive daughter isotope with adding horse photon isotope) or particular isotope (can launch positron with adding horse photon
Isotope (isotope), such as124I,86Y,89Zr etc.) decay when, detecting wink Fa Jiama photon and positron are mutually ruined plus horse photon
It is right.Because its positron emission core of above-mentioned radiation source has correlation with wink Fa Jiama distribution of photons.Therefore based on the distribution of PET activity
The previous message (prior information) of image reconstruction can be gulped down as Kang Pu after dosage association process.Image reconstruction mistake
Cheng Zhong, using positron emission core and wink Fa Jiama photon spatial distribution correlation, imaging calculation method is gulped down with the embedded Kang Pu of PET
Image reconstruction is carried out, may be such that possible position distribution where penetrating source wink Fa Jiama gulps down pyramidal plane by the Kang Pu of script and is contracted to
Maximum possible probability distribution region, the method, which can improve PG images signal to noise ratio and accelerate Kang Pu, gulps down image reconstruction speed.PET/PG
Difunctional imaging can take into account PET and wink Fa Jiama photon imaging advantage, can more improve proton or the checking of heavy ion range and agent
Measure the precision bestowed or the quality of core doctor's dual-isotope or particular isotope radiography.
The present invention provides a kind of plus horse photon detection device, and it is using the probe being made up of scintillation crystal.Pass through sudden strain of a muscle
Bright detection utensil has rapid time response (time response) characteristic, from respond fast scintillation crystal (such as LSO, LYSO,
LaBr3 etc.) arrange in pairs or groups Quick photoelectric sensor and pre-amplification circuit, the detection signal response time and temporal resolution of system can
Up to nanosecond grade.The present invention by same probe reach detecting positron mutually ruin caused by plus horse photon pair and because proton with
Nuclear inelastic collision is organized, excimer daughter nucleus to sharp state, the wink Fa Jiama photon of high-energy is produced in nanoseconds.This
The detecting probe of invention compares semiconductor detecting probe such as bilateral silicon strip type probe (DSSD), cadmium zinc tellurium type detecting probe
The microsecond response of (CdZnTe, CZT), the signal response time of nanosecond flicker detection system can shorten soon, with symbol time window
Hundreds times, detection counting rate can be lifted and the influence that non-true coincidence detecting counts is greatly reduced, and then lift proton range shadow
Image sharpness and bragg peak (Bragg peak) estimation accuracy.
The present invention provides a kind of plus horse photon detection method, utilizes with the difunctional design of a machine plus horse photon detection dress
Put, double radiography functions of the distribution of positron emission core and wink Fa Jiama photon are reached with same probe.This case is detectd using fast blink
Inspection device is that basis set is formed as popping one's head in, wink Fa Jiama photon radiography (prompt gamma imaging, PGI) pattern of two periods
The acquisition of radiography (positron annihilation imaging, PAI) mode data is mutually ruined with positron so that two-in-one detection
System has the function that detecting positron mutually ruins photon pair and wink Fa Jiama photon.Using this system, proton/heavy particle therapy is used
In-room PET can also have wink Fa Jiama photon detection imaging application.The proton/heavy ion beam treatment period (t0~
T1) detecting probe carries out data acquisition, t1~t2 periods after beam stops with wink Fa Jiama imaging PGI pattern, and probe is adopted just
Sub imaging PAI patterns of mutually ruining carry out data acquisition.The initial data obtained is through PET image reconstructions and the embedded image weights of PET
Build and obtain PET images and PG images respectively.Compare prior art single machine and single function energy and two-shipper is difunctional, a machine double-purpose of the invention
Way design, the function of in-room PET and the distribution of photons imaging of wink Fa Jiama can be had concurrently, it is not only economical convenient, also because fully sharp
Mutually ruined with wink Fa Jiama photon and positron and add horse photon spatial distribution relevance, image reconstruction is gulped down with the embedded Kang Pu of PET and melted
PET/PG slur pictures are closed, range is more improved and assesses precision.
In one embodiment, the present invention provides a kind of plus horse photon detection device, includes multiple detecting probes and one
Signal processing circuit.The plurality of detecting probe, each detecting probe have multilayer scintillation crystal detection device, detectd along corresponding
The axial direction arrangement of probing head, adjacent scintillation crystal detection utensil have a distance, and each detecting probe adds horse photon to capture
To produce corresponding electric signal.The signal processing circuit is electrically connected with the plurality of detecting probe, to obtain on one first
Electric signal caused by each detecting probe in period, and multiple scintillation crystals possessed by each detecting probe are detectd
News meet calculation when electric signal caused by inspection device carries out first, to interrogate phase when obtaining multiple the first of corresponding multiple detecting probes
Produced by pass data, and first layer scintillation crystal detection device of the acquirement on each detecting probe of this in a second time period
Electric signal, and news meet calculation during to carrying out one second, interrogate related data during obtaining multipair second.
In another embodiment, the present invention provides a kind of plus horse photon detection method, and it includes the following steps, carried first
For one plus horse photon detection device, it has at multiple detecting probes and the signal being electrically connected with the plurality of detecting probe
Circuit is managed, each detecting probe has a multilayer scintillation crystal detection device, and multilayer scintillation crystal detection device is along corresponding detecting
The axial direction arrangement of probe, adjacent scintillation crystal detection utensil have a distance.Then, the plurality of detecting probe one object of detecting is made
Caused plus horse photon.Then electric signal shape caused by each detecting probe of acquisition independent in a first time period
Into multiple first electric signal groups.Then, obtained with the signal processing circuit and detected on each in an at least first time period
Electric signal caused by probe, and to electric signal caused by multiple scintillation crystal detection devices possessed by each detecting probe
News meet calculation when carrying out first, meet related data to be interrogated when obtaining multiple the first of corresponding multiple detecting probes, and carry out
Storage；And telecommunications caused by the first layer scintillation crystal detection device of each detecting probe is captured in a second time period
Number, form multiple second electric signal groups and stored.Then, then with the signal processing circuit and obtain at least 1 the
Electric signal caused by the first layer scintillation crystal detection device of each detecting probe of this in two periods, and to carrying out one second
Shi Xun meets calculation, and news meet related data during obtaining multipair second.
Brief description of the drawings
Fig. 1 is the dose intensity and depth curve figure of charged particle and conventional photonic；
Fig. 2A is provided by the invention plus horse photon detection device embodiment configuration diagram；
Fig. 2 B to 2D are the different embodiment schematic diagrams of detecting probe of the present invention；
Fig. 2 E to Fig. 2 H are that the difference that the detecting probe of the present invention combines with arc track implements view；
Fig. 2 I to 2K are the different embodiment schematic diagrams of detecting probe of the present invention；
Fig. 3 A add horse photon detection method flow schematic diagram for the present invention's；
Fig. 3 B for the present invention capture detecting probe electric signal with when news meet calculation schematic flow sheet；
Embodiment schematic flow sheet is rebuild in the activity distribution that Fig. 3 C are the present invention；
Fig. 4 A to 4C are using Fig. 2A's plus horse photon detection device is detected wink Fa Jiama photon and positron and mutually ruined and adds horse
Photonic embodiment schematic diagram；
Fig. 5 gulps down scattered signal in different time sections acquisition Kang Pu for the present invention and PET adds horse photon signal schematic diagram；
News, which meet, when Fig. 6 is respectively from Fig. 7 calculates different embodiment schematic diagrams；
Fig. 8 A are that Kang Pu gulps down circular cone schematic diagram；
Fig. 8 B are then that the signal that image reconstruction previous message is gulped down as Kang Pu is distributed using the dosage based on PET images
Figure；
Kang Pus of the Fig. 9 between multiple probes gulps down circular cone and associates schematic diagram with the dosage distribution common factor based on PET images.
Description of reference numerals：2- adds horse photon detection device；20a, 20b, 20c, 20d, 20e- detecting probe；200a,
200b, 200c, 200d, 200e, 200f, 200g, 200h- scintillation crystal detection device；201- scintillation crystal arrays；202- photoelectric transfers
Sensor；203- reading circuits；204- is simulated and digital conversion circuit；205- optical fiber；21- signal processing circuits；22- rebuilds single
Member；220-PET rebuilds module；221- Kang Pu gulp down reconstruction module；222- the first activity distributed intelligences；223- dosage distributed intelligences；
224- the second activity distributed intelligences；23- authentication units；24- charged particle generation devices；25- plummers；26- arc tracks；3-
Add horse photon detection method；30~35- steps；340~343- steps；350~352- steps；8- charged particle beams；80、80’-
Kang Pu gulps down circular cone；81- activity is distributed；82a, 82b- region；9- objects；90th, 91- curves；910 bragg peaks；92- reacts position
Put.
Embodiment
Refer to shown in Fig. 2A, the figure is provided by the invention plus the embodiment configuration diagram of horse photon detection device.
In the present embodiment, should plus horse photon detection device 2 include multiple detecting probe 20a and 20b, a signal processing circuit 21,
One reconstruction unit 22 and an authentication unit 23.Each detecting probe 20a and 20b is the probe with nanosecond level of reaction,
It is detected face and mutually corresponded to, and is parallel to each other.Each detecting probe 20a and 20b has multilayer scintillation crystal detection device 200a
~200b and 200d~200e, arranged along the axial direction of corresponding detecting probe, adjacent scintillation crystal detection device 200a~200b
There is a distance with 200d~200e.In one embodiment, each detecting pops one's head in 20a and 20b to capture along a traveling side
To a charged particle beam caused by plus horse photon to produce corresponding electric signal.Each layer of scintillation crystal detection device 200a~
200b material is silicic acid lutetium (LSO) or the fast blink crystal such as yttrium luetcium silicate (LYSO) or lanthanum bromide (LaBr3), but not with this
For limitation.The charged particle beam is proton beam either HIB, and its caused mode is to utilize cyclotron
(cyclotron) or synchrotron (synchrotron) produces the charged particle beam of continous way or pulsed, is disliked to irradiate
Property tumour, by the maximum dosage of its bragg peak come tumors destroyed.In addition, in another embodiment, detecting probe 20a with
20b, which can also be used in particular isotope, (can launch positron with adding the isotope of horse photon, such as124I,86Y,89Zr etc.) decay when,
Detect its caused positron and mutually ruin and add horse photon pair and plus horse photon.In one embodiment, detecting probe 20a and 20b, it is
Kang Pu gulps down the framework of probe.
In one embodiment, as shown in Figure 2 B, each layer of scintillation crystal detection device 200a~200b has a flicker respectively
Crystal array 201 is connected to a photoelectric sensor 202 and the reading circuit 203 with pre-amplification circuit so that system is detectd
Signal response time and temporal resolution are examined up to nanosecond grade.In one embodiment, scintillation crystal array 201 is by multiple flickers
Crystal 201a is formed, and the photoelectric sensor 202 is the position sensitive photomultiplier (position-sensitive of how positive level
Photomultiplier tube, PSPMT) design, the optical signal scintillation crystal array 201 to be received is converted into simulating
Electric signal.In addition, photoelectric sensor 202 can also be photomultiplier (photomultiplier tube, PMT) or silicon
Photomultiplier transit element (silicon photomultiplier, Si-PM) array.The reading circuit 203 is to by photoelectric sensor
The 202 current signal shuntings exported, amplify and be converted to analog voltage signal.
In addition, as shown in Figure 2 C, it is another embodiment schematic diagram of scintillation crystal detection device.The He of scintillation crystal array 201
It is to be conducted by optical fiber 205 between photoelectric sensor 202, angle is had between scintillation crystal array 201 and photoelectric sensor 202
In the presence of.As shown in Figure 2 D, it is three layers of detection device schematic diagram, glitch caused by can reducing following reason by fiber optic conduction-
Extra Kang Pu caused by photomultiplier gulps down scattered photon, scattered photon caused by scintillation crystal before next layer of detection device is reached
Had an effect with photomultiplier.Alternatively, it is also possible to be reduced as far as the distance between detection layer and detection layer, geometry is lifted
Efficiency.Return shown in Fig. 2A, the analog electrical signal that each detecting probe 20a and 20b is exported is again by an integration and simulation
Turn digital circuit 204, the analog electrical signal of output is converted into digital electric signal.The signal processing circuit 21, itself and this
Integration and analog-to-digital circuit 204 are electrically connected with, to receive the digital electric signal.In one embodiment, the signal transacting
There is a FPGA (Field Programmable Gate Array) programmable circuit in circuit 21, it can pass through program pair
Received electric signal calculates, such as：Shi Xun meets calculation, and the transmission of the output data of circuit 21 is stored in into calculating afterwards
Machine hard disk or internal memory, to be used as subsequent reconstruction unit 22.In the present embodiment, signal processing circuit 21 is obtained on one first
Electric signal caused by each detecting probe in period, and multilayer scintillation crystal possessed by each detecting probe is detectd
News meet calculation when electric signal caused by inspection device carries out first, to interrogate phase when obtaining multiple the first of corresponding multiple detecting probes
Produced by pass data, and first layer scintillation crystal detection device of the acquirement on each detecting probe of this in a second time period
Electric signal, and news meet calculation during to carrying out one second, interrogate related data during obtaining multipair second.Wherein, so-called first
Shi Xun meets calculation, and news meet calculation when referring to do signal obtained by each layer of scintillation crystal detection device, each to judge
Whether the electric signal that each layer scintillation crystal detection device of individual detecting probe is detected comes from same plus horse photon, that is, wink is sent out
Add horse photon.In the present embodiment, so that 20a is popped one's head in detecting as an example, some adds horse photon first and first layer scintillation crystal detection device
After 200a effects, caused scattered photon acts on second layer scintillation crystal detection device 200b again, and both have the time slightly first
Difference afterwards, therefore, news meet calculation when first, just refer to each layer of scintillation crystal detection device 200a, 200b or 200d, 200e
News meet calculation when resulting signal is done, and then sentence and be to the electric signal by each layer of scintillation crystal detection device 200a, 200b
No is to belong to same plus horse photon event, and whether each layer of scintillation crystal detection device 200d, 200e belong to same plus horse
The event of photon.And news meet calculation when second, then refer to mutually to ruin positron and electronics caused by add in pairs horse photon respectively with
Calculated with respect to electric signal caused by the first layer detection device effect of detection probe, to judge the of each detecting probe
The electric signal that one layer of scintillation crystal detection device is detected whether come from a pair plus horse photon, that is, paired positron with
Electronics adds horse photon caused by mutually ruining.For example, in the present embodiment, paired plus horse photon is popped one's head in 20a with paired detecting respectively
With 20b first layer scintillation crystal detection device 200a, electric signal caused by 200d effects, then match operation is interrogated during by second
Afterwards, can differentiate 200a, 200d whether be same group of positron with electronics mutually ruin caused by produced by a pair plus the effect of horse photon
Electric signal.
Foregoing detecting probe is all the combination for the detection device for belonging to top surface illuminaton (top-on), in another embodiment
In, detecting probe can also be the combination of side-irradiation type (side on) and top surface illuminaton.For example, shown in Fig. 2 I, detecting
Probe 20c has two scintillation crystals detection device 200a and 200f, and wherein scintillation crystal detection device 200a is top surface illuminaton
(top-on) detection device, and scintillation crystal detection device 200f is the detection device of side-irradiation type.In addition, as shown in fig. 2j, detect
Probing head 20d has two scintillation crystals detection device 200f and 200g, is all the detection device for belonging to side-irradiation type.In addition, will
Illustrate, the photoelectric sensor 202 at the detection device both ends of side-irradiation type can be arranged on the both ends of scintillation crystal, such as Fig. 2 I
It is shown, or single end, as shown in figure 2k, it can be depending on the demand of user.
Reconstruction unit 22, in one embodiment, it is arranged on a computer or has in the system of calculation processing power, it is wrapped
PET is included and rebuilds module 220 and Kang Pu and gulp down and rebuild module 221, to from the storage device or internal memory for being stored in hard disc of computer
Related data is interrogated when taking out first and second.Wherein, the Kang Pu, which is gulped down, rebuilds the processing of module 221 under PGI patterns, detecting probe
20a and 20b are in proton/heavy particle beam therapy period (t0~t1) sensing wink Fa Jiama photon and caused data.As for PET
Rebuild 220 modules then to handle under PAI patterns, detecting probe 20a and 20b t1~t2 periods after treatment beam stops are picked
The paired 511keV energy taken adds data caused by horse photon.PET rebuilds the first activity distribution letter obtained by 220 remodellings
Breath 222 further carries out a reflexed product (deconvolution) processing, after obtaining dose distributed intelligence 223, then is transmitted to
Kang Pu, which is gulped down, rebuilds module 221 so that Kang Pu, which gulps down reconstruction module 221, to be distributed the first dosage as previous message, and rebuilds
The second activity distributed intelligence 224 on wink Fa Jiama photon is obtained, and then evaluates the reality of charged particle in vivo
Range.The difunctional imagings of PET/PG can take into account PET and wink Fa Jiama photon imaging advantage, can more improve proton or heavy particle is penetrated
The precision that journey is verified and dosage is bestowed.In a radiotherapy Application Example, the reconstruction unit 22 can be with an authentication unit
23 connections, after the authentication unit 23 receives the activity distribution that reconstruction unit 22 is exported, the authentication unit 23 passes through PET and PG
Activity distribution, establish and show charged particle in vivo actual dose range distribution, to provide medical practitioner
Practical range result and the comparison and confirmation for the treatment of plan prediction range are carried out, and then using the difference as charged particle next time
The foundation of radiation parameters amendment.In addition, in one embodiment, horse photon detection imaging device 2 should be added to have more a charged particle
Generation device 24, it can be treated and synchronous carry out live body Treatment monitoring plus horse photon detection device with being formed, this is powered
Particle generating device 24 treats required charged particle to produce.
As shown in Figure 2 E, in one embodiment, the plurality of detecting probe 20a and 20b is arranged on the track 26 of an arc,
Can be in the enterprising line position shifting movement of the arc track 26 so that detecting probe 20a or 20b can be rotated with a center, to adjust
The position of its whole detecting, the present embodiment rotate using the center of arc track 26 as rotating shaft.It is noted that because the present invention has
There is the function of PET and PG detecting imagings, therefore under PET imaging modes, each detecting probe 20a and 20b must be relative 180
Degree configuration, and under PG imaging modes, detecting probe 20a or 20b side can be any angle.In another embodiment, such as Fig. 2 F
It is shown, when the charged particle generation device 24 produces charged particle 8, there is an angle between detecting probe 20a and 20b, its is big
In 0 degree, the present embodiment is 90 degree or so, to increase the uniformity of wink Fa Jiama photon image three-dimensional resolution ratio.In addition to illustrate
Although the detecting probe in Fig. 2A, 2E and 2F is a pair, system is not limited, it can be according to the demand used, example
Such as：Resolution ratio, cost etc. consider, set required quantity, such as：In fig 2g, there are two groups of detecting modules, each is detectd
Surveying module has multiple detecting probe 20a, 20c, 20e and 20b, 20d, 20f.In addition, as illustrated in figure 2h, each detecting is visited
Head 20a and 20b itself can also be rotated for axle and the translational movement towards or away from the center of circle.
Refer to shown in Fig. 3 A, the figure be the present invention plus horse photon detection method flow schematic diagram.In the present embodiment,
This method 3 includes the following steps：Step 30 is carried out first, and one is anti-according to possessed by determining in an object photon detection
Answer position.In this step, an embodiment of the photon detection is in order to carry out the computed tomography that treatment plan is implemented
(computed tomography, CT), its mainly by X-ray to organism, such as：Human body, it is scanned, the human body is
The object, the response location, it is tumour in an embodiment.Determine the position of tumour by computerized tomography.It has found anti-
After answering position, step 31 is carried out, according to the situation of organism, such as：The soft tissue distribution of surrounding, and response location letter
Breath, is converted into a radiation parameters of charged particle beam, it includes the energy of irradiation, dosage and direct of travel and depth.Cause
It is the spatial distribution for belonging to three dimensionality in object for response location, therefore as charged particle beam is projected to the row of object
Enter depth difference, energy needed for it also can difference.It is noted that the direct of travel and depth of charged particle beam, and
Can not have multiple direct of travels and depth according to the demand for the treatment of with single for limitation, that is, from more directions with it is more
Individual range depth is exposed on the response location.
Charged particle in the present embodiment is proton, because the dosage that proton initially discharges into sufferer body surface is at a fairly low,
Until certain range depth, proton kinetic energy produces maximum dose deposition after declining to a great extent, and corresponding to this range depth
Releasing dosage is referred to as bragg peak, almost complete absence of dosage (as shown in Figure 1) after bragg peak.And step 31 basis
The energy or dosage that response location determines, be using this characteristic, by the regulation and control of proton energy and proton range by dosage most
High bragg peak falls, in target location area, to make the normal structure at response location rear can then avoid radiation exposure risk.
After step 31, step 32 is then carried out, in this step, there is provided as shown in Figure 4 adds horse photon detection device
2.The dosage or energy determined in order to ensure step 31 can concentrate on the position corresponding to bragg peak, therefore in treatment
During, it can be monitored by provided by the invention plus horse photon detection device 2 to carry out the synchronous live body of real-time, to ensure
The efficiency and reduction error for the treatment of, and then normal structure can be protected from the injury of radiation.As shown in Figure 4 A, object 9
For an organism, lie low on plummer 25, there is response location 92 in object 9, the present embodiment is tumour.Multiple detectings are visited
First 20 rings are located at the periphery of object 9, though the present embodiment has two detecting probe 20a and 20b, its quantity can be according to need
Depending on asking.Carry out step 33 again afterwards, the charged particle generation device 24 is produced a charged particle beam 8.When in therapeutic process,
Information is irradiated according to caused by step 31, after projection charged particle beam 8 projects towards object 9, is entered in object,
Proton is that proton is made with sufferer tissue with after the nuclear inelastic collision of tissue, can mainly produce two kinds plus horse photon, one kind
A pair of 511keV energy of generation are mutually ruined with caused offspring-positron caused by positron emission nuclear decay and the electronics in tissue
Amount adds horse photon.Another kind is that target nucleus is excited to sharp state when inelastic collision occurs for proton and tissue atomic nucleus,
Wink Fa Jiama photon is produced in nanoseconds.
Add horse photon to detect both, detectd by step 34 in a period with first time period with second time period
Survey and capture electric signal.For producing this implementation of charged particle, the first time period represents the period of charged particle startup,
The second time period then represents the period of charged particle closing.As shown in Figure 4 A, in the first of the startup of charged particle beam 8
Between in section, each detecting probe 20a and 20b each layer scintillation crystal detection device 200a and 200b and 200d and 200e, meeting
The signal of wink Fa Jiama photon incidence is detected, so that 20a is popped one's head in detecting as an example, that is, some adds horse photon first to be sparkled with first layer
After crystal detection device 200a effects, caused scattered photon sparkles crystal detection device 200b effects with the second layer again, and both have slightly
Time order and function difference, similarly, detecting probe 20b be also such.Conversely, as shown in Figure 4 B, closed in charged particle beam 8 the
In two periods, each detecting probe 20a and 20b first layer scintillation crystal detection device 200a and 200d, can detect because
The incident signal of caused paired plus horse photon is mutually ruined for positron, that is, positron mutually ruins caused paired plus horse with electronics
Photon can respectively with relative detection probe 20a and 20b first layer scintillation crystal detection device 200a and 200d effect.It is segmented and detects
The main cause of survey is only to be produced because of wink Fa Jiama photon in the period of charged particle starts, and existence time is relatively brief,
Otherwise positron mutually ruins plus horse photon then reaction time length, therefore two kinds add the characteristic of horse photon different.Mutually ruined in addition, measuring positron
Horse photon is added separately to measure wink Fa Jiama light to having had clinical practice maturity with PET activity image estimation charged particle range
Subsignal and positron mutually ruin plus horse photon pair, can pass through more ripe PET skill upgrading wink Fa Jiama photons image weights
The accuracy built, and the signal of wink Fa Jiama photon be positron mutually ruin plus horse photon decades of times, wink Fa Jiama photon radiography can
The signal to noise ratio of image is lifted, and then strengthens the precision of charged particle range checking application.It is noted that although Fig. 4 B are just
Son is to being sensed by first layer scintillation crystal detection device 200a and 200d, in another embodiment, as shown in Figure 4 C, according to this
Positron by the scintillation crystal detection device 200b and 200e of the second layer to can also be sensed.
Refer to shown in Fig. 3 B, in step 34, it is each to further include step 340 acquisition independent in first time period
Electric signal caused by individual detecting probe 20a and 20b, form two groups of corresponding detecting probe 20a and 20b the first electric signal group.
In this step, so that 20a is popped one's head in detecting as an example, the signal processing circuit 21 is recorded respectively and add horse photon E accordingly0
Kang Pu occurs with first layer scintillation crystal detection device 200a and gulps down the first position, that scattering (Compton scattering) acts on
One time and the first sedimentary energy Δ E and scattering plus horse photon energy E1With second layer scintillation crystal detection device 200b effects
The second place, the second sedimentary energy Δ E2With the second time, to form the first foregoing electric signal group.Ideally the second layer flashes
Crystal detection device 200b fully absorbs scattering plus horse photon energy E1, so the second sedimentary energy Δ E2=E1.And then with step
Multiple first electric signal groups caused by probe are detected on each in the first time period in rapid 341 acquisition step 340,
And interrogate to meet when carrying out first to electric signal caused by multiple scintillation crystal detection devices possessed by each detecting probe and drill
Calculate, filter non-real onrelevant signal, it is related to be interrogated when obtaining multiple wink Fa Jiama photons the first of corresponding multiple detecting probes
Data.Step 340 is illustrated with Fig. 6, news meet calculation schematic diagram when it is first.So that 20a is popped one's head in detecting as an example, it is had
First had is to second layer scintillation crystal detection device 200a~200b, and the signal corresponding to the event detected respectively takes out, Fig. 6 institutes
It is shown as three events I1, I2, I3.Each event has two electric signals, corresponds to each layer of scintillation crystal detection device respectively
200a~200b, each group of electric signal contain the information of position, time and energy.Believed again by comparing first and second time
Number, such as fall meeting in time window in setting, then it represents that second layer scintillation crystal detection device measurement gained electric signal comes from
It is big with the effect of first layer scintillation crystal detection device plus horse photon chance.In the present embodiment, there are three same time windows
Period W1, W2 and the W3 of width, it is to be noted that, the size of time window can determine the length of time window according to demand
Degree.From fig. 6, it can be seen that in W2 period, only scintillation crystal detection device 200a has signal, and scintillation crystal detection device 200b is then
Nothing, and then scintillation crystal detection device 200a and 200b have signal simultaneously in period W1 and W3, therefore represent W1 the and W3 periods and pick
The signal that meets is interrogated when the signal taken belongs to, that is, ascertain whether for same group incidence wink Fa Jiama photons and its scattering plus horse light
Electric signal caused by son.In this way, then record is stored, is not such as otherwise stored record.
Then step 342 is carried out, that is, each detecting probe 20a and 20b first layer is captured in second time period
Electric signal caused by scintillation crystal detection device 200a and 200d, form multiple second electric signal groups.It is main in this step 342
If handle the signal processing circuit 21 and digitize to add horse photon representing first layer scintillation crystal obtained by detecting probe 20a
The first positions of detection device 200a effects, the very first time and the first sedimentary energy and add horse photon the of detecting probe 20b
The second place, the second sedimentary energy and the second time of one layer of scintillation crystal detection device 200d effect, to form foregoing second
Electric signal group.As shown in figure 5, from t0~t2, in the first time period of t0~t1 during the detecting, step during wherein detecting
Multiple electric signal group B1 of the multiple electric signal group A1 and detecting probe 20b on detecting probe 20a can be obtained in rapid 340,
Similarly in t1~t2 second time period, performing step 341 can then obtain on each detecting probe 20a with being had in 20b
First layer scintillation crystal detection device 200a and 200d obtained by multigroup electric signal C1.PET flicker detections are cured according to existing core
Device designs, and by detection device circuit for detecting signal, then can learn plus horse photon is acted on which scintillation crystal, and then learn
Active position and time of origin, then the time for detecting signal is recorded, being deposited on the energy of detection device equally can be by
Corresponding electrical signal intensity is learnt.Therefore, each signal Pa1~Pan, Pb1~Pbn, Pd1~Pdn contain with Pe1~Pen
The information of position, time and sedimentary energy.
And then carry out in step 343 acquisition step 342 on this in the second time period each detecting probe the
Multiple second electric signal groups caused by one layer of scintillation crystal detection device, and meet calculation to being interrogated during progress one second, filtering is non-
Genuine onrelevant signal, related data is interrogated during obtaining multipair second.In this step, the object that news meet calculation when is each
The first layer scintillation crystal detection device of individual detecting probe, it is that the scintillation crystal for detecting probe 20a and 20b is detectd by taking Fig. 4 A as an example
Examine device 200a and 200d.Refer to shown in Fig. 7, it is in the figure 7 it is shown that right produced by scintillation crystal detection device 200a and 200d
Should have three event I4~I6 multiple second electric signal groups, in the present embodiment, by three same time window widths when
Section W4~W6 and energy come confirm these signals whether belong to same positron mutually ruin caused by a pair of 511keV's plus horse
A pair of electric signals caused by photon.In this way, then record is stored, is not such as otherwise stored record.It is noted that
In another embodiment, step 340~341 and step 342~343 can be carried out with independent synchronization.
Return shown in Fig. 3 A, after step 34, further can be walked using the reconstruction unit 22 shown in Fig. 4 A
Rapid 35 activity distribution is rebuild, and then the result that last activity is distributed is converted into image.The basis that this step is rebuild is to utilize
PET activity is distributed the previous message that imaging is gulped down as Kang Pu, and then carries out Kang Pu again and gulp down image reconstruction.Because the matter in patient
Son or heavy ion range approach also produce wink Fa Jiama photon, so positron emission core and proton in addition to positron emission core is produced
Or the distribution of heavy ion dosage is relevant, also has correlation with wink Fa Jiama distribution of photons.Therefore through dosage based on the distribution of PET activity
The previous message of image reconstruction can be gulped down after association process as Kang Pu.As shown in Figure 3 C, step 350 is carried out first, first by step
Obtained by 343 second when news meet data and first carry out preposition processing, include the position letter of the correction of detection device, the output of detection device
Number produce and associate with crystal positions, be converted into position and energy datum and carry out PET reconstructions, obtain mutually ruining on positron and add horse photon
The first activity distribution.The proton or heavy ion range approach that positron is mutually ruined plus the activity of horse photon is distributed in cooperation patient exist
The distribution of substantially rectilinear beam in space, its represent according to positron mutually ruin plus horse photon obtained by charged particle beam
Incident range situation.Then carry out step 351 and the positron in step 350 is mutually ruined to the first activity distribution reconvert for adding horse photon
To estimate the dosage distributed intelligence obtained by PET.Finally progress step 352, which mutually ruins the positron obtained by step 351, adds horse light
The dosage distributed intelligence of son is associated, that is, using the dosage distributed intelligence of step 351 as the previous message of step 352,
Carry out the embedded Kang Pu of PET and gulp down image reconstruction, be also that Kang Pu is gulped down circular conical surface and mutually ruined by positron with abovementioned steps 351 to add horse photon
Activity distribution conversion estimation obtain dosage distributionOccured simultaneously, further to obtain the distribution of one second activity.
Explanation is using the principle of step 352 below, and as shown in Figure 8 A and 8 B, Fig. 8 A are that will represent wink Fa Jiama light merely
Son and the active position of detection device and the electric signal of sedimentary energy, if for example, telecommunications with the single incident obtained by step 343
Number, such as：Pa1 and Pb1 in Fig. 6, preposition processing is carried out, such as：Include the position letter of the correction of detection device, the output of detection device
Number with crystal positions produce associate, rebuild again afterwards to obtain activity distribution map.Scattering principle, Ke Yicong are gulped down according to Kang Pu
Incidence flicker detection device plus horse photon and scattering plus horse photon between possessed angle of scattering come estimate produce plus horse light
The possibility originated location of son.Calculation among this, can using when news meet calculation to carry out incident and scattering plus horse photon
Pairing.Meet calculation processing by being interrogated during step 341 to be interrelated from first layer and second layer scintillation crystal detection device
Together plus horse photon, according to the energy and equation (1) that detect can learn produce plus horse photon originate from can
Can region.
Where E0=E1+ΔE1
Wherein, primary energy E0High energy add horse photon and first layer to flash detection device 200a and 200d and produce Kang Pu to gulp down
Scattering process, release portion of energy Δ E1It is E after first layer flashes detection device1The Kang Pu of energy gulps down scattered photon.To being measured
For sending out gamma rays to single wink, the possible position of this originating point is distributed in a Kang Pu and gulps down circular cone (Compton cone) 80
Surface.However, because Kang Pu gulps down circular cone 80, active position (summit) and scatteringangleθ can only be known, as long as therefore on the conical surface
Any one position be likely to be the position where object, therefore only gulp down circular cone using Kang Pu to infer target merely
The position at place, its uncertain still high monitoring for being unfavorable for treating range.In order to solve this problem, step 351 is employed
With reference to the mode of step 352, that is, using proton or heavy ion, range approach produces offspring-positron hair in patient
Penetrate core and wink Fa Jiama photon, thus positron emission core with wink Fa Jiama distribution of photons with proton/heavy ion range and dosage
Related characteristic, dosage distribution is converted into after dosage association process based on the distribution of PET activity, to be gulped down into as Kang Pu
The previous message of picture is distributed to rebuild activity.In this embodiment, the positron emission formed by PET images after step 351
Core activity is distributedIt is converted into dosage distributionThe mode of conversion can use such as filter function reflexed product side
Method conversion positron emission core activity be distributed as dosage distribution (S.Remmele et.al.2011Phys.Med.Biol.), but not with
This is limited.As shown in Figure 8 B, the line beam of wherein label 81 represents the dosage spatial distribution estimated by PET imagesItself and Kang Pu gulp down the common factor of conical surface 80 and constitute one or two region 82a and 82b.Then most possible wink Fa Jiama
Photon originated location gulps down the surface of circular cone 80 by Kang Pu and is contracted to region 82a and 82b, and now most possible wink Fa Jiama photon rises
Source positionIt can be represented with following formula,
Then in step 352, after common factor, single wink Fa Jiama photons origin possible position distribution can be by original
This Kang Pu gulps down the surface of circular cone 80 and is contracted to region 82a and 82b.During the embedded Kang Pu of PET gulp down image reconstruction, the source of penetrating can
Can position distribution range shorter by be greatly improved rebuild after image signal to noise ratio quality, this can not only accelerate wink Fa Jiama photon
Image reconstruction convergence rate, it is often more important that the precision that lifting range is assessed.
Be in the fig. 8b step 343 second when interrogate related data through step 350~351 PET image reconstructions and dosage
Distribution after conversion and step 341 first when the news related data activity distribution that is formed through step 352 occur simultaneously
As a result.Because Fig. 4 A embodiment has two detecting probe 20a and 20b, therefore for each detecting probe 20a and 20b in step
Activity distribution as shown in Figure 9 is formed after rapid 353 to occur simultaneously.Circular cone is gulped down by the Kang Pu for detecting probe 20a and detecting probe 20b
What 80 and 80 ' and detecting probe 20a and detecting probe 20b first layer scintillation crystal detection device 200a and 200d were formed
PET frameworks, the distribution 81 after activity distribution and dosage conversion obtained by it are occured simultaneously and horse photon possible position can will be added to be contracted to
The region of common factor, and then lift follow-up range and assess precision.
By taking oncotherapy as an example, because treatment plan assessment can be carried out before treatment, position, the band electrochondria of tumour are assessed
Angle that beamlet should irradiate and the dosage bestowed etc..In order to confirm in therapeutic process, the reality of charged particle beam in vivo
Range estimates the difference of range with the position and treatment plan for producing bragg peak, and therefore, device of the invention and method can
To obtain the practical range of charged particle beam in real time in each treatment, the information of display, Ke Yirang are provided by authentication unit 23
The range of user's checking comparison therapy Program Assessment is distributed the difference of determined practical range with the activity as caused by step 352
It is different, and then adjust as successive treatment the foundation of the charged particle beam irradiation parameter, so can reach live body treatment monitoring with
The double effectses suggested are adjusted, the validity for the treatment of is lifted and reduction damages the secondary of health tissues because range is uncertain and made
With.
Foregoing embodiment is the embodiment with two layers of scintillation crystal, in another embodiment, can be with three layers
Scintillation crystal, structure as shown in Figure 2 D, be provided with third layer scintillation crystal detection device purpose be consider Kang Pu gulp down it is scattered
It is excessively preferable to penetrate two layers of scintillation crystal detection device detection device design of imaging, because second layer detection device (also known as absorbs detection
Device) all energy for obtaining scattered photon must be mended, could obtain equation (1) or needed for equation (2) plus horse photon it is initial
ENERGY E0.So because the wink Fa Jiama photon energy that proton therapeutic induces has a very wide distribution and energy is high, general energy is in several keV
To 10MeV, even up to 15MeV.Therefore, initial plus horse photon energy during actual detecting is unknown, and scatters and add horse photon energy
Measure E1The probability all stopped by absorption detection device is limited, wants to pass through E1And it is deposited on the energy Δ E of first layer detection device1It is total
Initially add the full ENERGY E of horse photon with knowing0Chance it is not high.In order to strengthen this part, in the present embodiment, detecting is popped one's head in
Use three layers of flicker detection device design instead, the detection device only requirement of third layer measures the active position but nothing of second scattered photon
The sedimentary energy of third layer detection device need to be recorded.θ2The incidence that can each be recorded by three scintillation crystal detection devices of calculating
Add horse photon to be obtained with scattering plus horse photon position, the record substitution of all known energies can be calculated into incident light component afterwards
Possible position (be also caused by proton and function of organization wink Fa Jiama photon original position) where Kang Pu gulp down coning angle
θ1, as shown in equation (3).As for the embedded image reconstructions of PET of step 361, three layers flash under detection device situations herein, most
Possible wink Fa Jiama photon originated locationsIt is still to be calculated by equation (2).
E0=E1+ΔE1
E1=E2+ΔE2
In addition, it is noted that in foregoing embodiment, for caused by detecting charged particle beam wink Fa Jiama photon with
And paired positron mutually ruins plus horse photon.In another embodiment, arrangement for detecting of the invention can also be applied in nucleon medical science
Dual-isotope (mix positive daughter isotope with plus horse photon isotope) or particular isotope (can launch positron with plus horse photon
Isotope, such as124I,86Y,89Zr etc.) radiography etc..Therefore, horse photon is not added to be limited caused by charged particle beam to detect
System.In the present embodiment, similarly, first time period detecting plus horse photon, second time period then detect positron is mutually ruined plus horse
Photon, first and second such period, alternately the electric signal of acquirement was handled according to the step of Fig. 3 B and Fig. 3 C,
And then activity distribution and image corresponding to reconstructing.
The better embodiment or reality described above for only recording technological means used by the present invention solves the problems, such as presentation
Example is applied, is not used for limiting the scope of patent working of the present invention.It is i.e. all to be consistent with present patent application scope context, or
The equivalent changes and modifications done according to the scope of the claims of the present invention, it is all that protection scope of the present invention is covered.
Claims (21)
1. one kind plus horse photon detection device, it is characterised in that including：
Multiple detecting probes, each detecting probe have multilayer scintillation crystal detection device, each layer of scintillation crystal detection device edge
The axial direction arrangement of detecting probe corresponding to, adjacent layer scintillation crystal detection utensil have a distance, each detecting probe to
Capture and add horse photon to produce corresponding electric signal；And
One signal processing circuit, it is electrically connected with the plurality of detecting probe, to obtain on each in a first time period
Electric signal caused by detecting probe, and to electricity caused by multilayer scintillation crystal detection device possessed by each detecting probe
News meet calculation when signal carries out first, to judge that each detects the electricity that each layer scintillation crystal detection device popped one's head in is detected
Whether signal comes from same plus horse photon, to interrogate related data when obtaining multiple the first of corresponding multiple detecting probes, and
Obtain on electric signal caused by the first layer scintillation crystal detection device of each detecting probe of this in a second time period, and
News meet calculation during to carrying out one second, interrogate related data during obtaining multipair second, with judge that each detecting pops one's head in the
The electric signal that one layer of scintillation crystal detection device is detected whether come from a pair plus horse photon.
2. add horse photon detection device as claimed in claim 1, it is characterised in that with more a reconstruction unit, to basis
This multipair secondth when interrogate related data rebuild one first activity distribution, then by first activity distribution carry out one conversion after
It is distributed to dosage, then dosage distribution is associated with interrogating related data when the plurality of first with reconstruction one second activity distribution.
3. add horse photon detection device as claimed in claim 1, it is characterised in that it is at least one isotope that should add horse photon
Via produced by a degeneracy function.
4. as claimed in claim 1 plus horse photon detection device, it is characterised in that with more a charged particle generation device,
To produce a charged particle, the charged particle beam produces when being acted on along a direct of travel and an object should add horse photon.
5. add horse photon detection device as claimed in claim 4, it is characterised in that the first time period is that the charged particle opens
Dynamic period, each detecting probe detecting add horse photon to be wink Fa Jiama photon, and the second time period is the band electrochondria
The period that son is closed, each detecting probe add horse photon to detect paired positron and mutually ruin.
6. as claimed in claim 4 plus horse photon detection device, it is characterised in that the charged particle beam be proton or again from
Son.
7. as claimed in claim 1 plus horse photon detection device, it is characterised in that the plurality of probe can be independently with one
Heart position is rotated or relatively moved, to change detecting position.
8. add horse photon detection device as claimed in claim 1, it is characterised in that each layer of scintillation crystal detection device further includes
Have：
One scintillation crystal array；
One photoelectric sensor, coupled with the scintillation crystal, optical signal caused by scintillation crystal array is converted into telecommunications
Number；And
One reading circuit, comprising pre-amplification circuit, it is electrically connected with the photoelectric sensor.
9. add horse photon detection device as claimed in claim 8, it is characterised in that the scintillation crystal array is by optical fiber with being somebody's turn to do
Photoelectric sensor couples.
10. add horse photon detection device as claimed in claim 8, it is characterised in that the scintillation crystal array is that side is irradiated
Formula scintillation crystal array either front illuminated formula scintillation crystal array.
11. one kind plus horse photon detection method, it is characterised in that comprise the following steps：
One plus horse photon detection device are provided, it has multiple detecting probes and be electrically connected with the plurality of detecting probe one
Signal processing circuit, each detecting probe have a multilayer scintillation crystal detection device, and each layer of scintillation crystal detection device is along right
The axial direction arrangement for the detecting probe answered, adjacent layer scintillation crystal detection utensil have a distance；
Add horse photon caused by the plurality of detecting probe one object of detecting；
The electric signal of detecting probe is captured during one, wherein during this period by a first time period and a second time period group
Into；
Obtain on electric signal caused by each detecting probe in the first time period, and had to each detecting probe
News meet calculation when electric signal caused by some multilayer scintillation crystal detection devices carries out first, are visited with obtaining corresponding multiple detectings
Head multiple first when interrogate related data；And
Obtain on telecommunications caused by the first layer scintillation crystal detection device of each detecting probe of this in the second time period
Number, and news meet calculation during to carrying out one second, interrogate related data during obtaining multipair second.
12. add horse photon detection method as claimed in claim 11, it is characterised in that further included using a reconstruction unit root
According to this multipair second when interrogate related data rebuild one first activity distribution, then by first activity distribution carry out one conversion after
To dosage be distributed, then by the dosage be distributed with when the plurality of first interrogate related data it is associated with rebuild one second activity be distributed
Step.
13. add horse photon detection method as claimed in claim 11, it is characterised in that horse photon should be added at least one same position
Element is via produced by a degeneracy function.
14. add horse photon detection method as claimed in claim 11, it is characterised in that it is a charged particle beam that should add horse photon
Along produced by a direct of travel and object effect, the corresponding maximum range of a radiation parameters of the charged particle beam assesses position
Put.
15. add horse photon detection method as claimed in claim 14, it is characterised in that the first time period is the charged particle
The period of startup, each detecting probe detecting wink Fa Jiama photon, the second time period is the period that the charged particle is closed,
Each detecting probe detecting positron mutually ruins plus horse photon.
16. as claimed in claim 14 plus horse photon detection method, it is characterised in that the charged particle beam be proton or again from
Son.
17. add horse photon detection method as claimed in claim 11, it is characterised in that capture electric signal in the first time period
The following steps are further included：
Multilayer scintillation crystal detection device in each detecting probe is detected on wink Fa Jiama photon and its scattering plus horse light respectively
Two events of son；And
Electric signal caused by multilayer scintillation crystal detection device in same detecting probe is handled, it is more on this to obtain
Multiple first digital electric signals of layer scintillation crystal detection device.
18. as claimed in claim 17 plus horse photon detection method, it is characterised in that in this first when news meet calculation more wrap
The following steps are included：
Obtain multiple first digital electric signals on the multilayer scintillation crystal detection device；And
With a time window sequentially compare the multilayer scintillation crystal detection device in each detecting probe caused by difference it is multiple
First digital electric signal, if the time difference of the first digital signal of different layers scintillation crystal detection device fall in setting when meeting
Between in window, then it represents that different layers scintillation crystal detection device measurement the first data signal of gained comes from first layer scintillation crystal
The effect of detection device adds horse photon.
19. add horse photon detection method as claimed in claim 11, it is characterised in that the second time period captures electric signal more
Include the following steps：
A first layer scintillation crystal detection device in each detecting probe is detected positron and mutually ruined respectively adds horse photo-event；And
Electric signal caused by first layer scintillation crystal detection device in each detecting probe is handled, to obtain on every
Multiple second digital electric signals of one first layer scintillation crystal detection device.
20. as claimed in claim 19 plus horse photon detection method, it is characterised in that in this second when news meet calculation more wrap
The following steps are included：
Obtain multiple second digital electric signals of the first layer scintillation crystal detection device on different detecting probes；And
With a time window sequentially compare the first layer scintillation crystal detection device in each detecting probe caused by difference it is more
Individual second digital electric signal, if the first layer scintillation crystal detection device in different detecting probe distinguish caused by second count
The word electric signal time difference falls the second digital electric signal its energy met in time window and in the time window in setting
In default energy range, then it represents that each first layer scintillation crystal detection device measurement the second digital electric signal of gained is from same
One positron adds horse photon pair caused by mutually ruining.
21. add horse photon detection method as claimed in claim 11, it is characterised in that each scintillation crystal detection device more wraps
Include：
One scintillation crystal array；
One photoelectric sensor, coupled with the scintillation crystal, light news caused by scintillation crystal array are converted into electric signal；
And
One reading circuit, comprising pre-amplification circuit, the pre-amplification circuit is electrically connected with the photoelectric sensor, the wherein sudden strain of a muscle
Bright crystal array is side-irradiation type scintillation crystal array either front illuminated formula scintillation crystal array.
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| TW105120636A TWI599790B (en) | 2016-06-29 | 2016-06-29 | Apparatus and method for imaging gamma ray |
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| CN108957517A (en) * | 2018-06-15 | 2018-12-07 | 中派科技（深圳）有限责任公司 | Detector and Positron emission tomography equipment for Positron emission tomography equipment |
| CN110133013A (en) * | 2018-02-02 | 2019-08-16 | 西门子医疗有限公司 | Detector module |
| CN110477942A (en) * | 2019-08-20 | 2019-11-22 | 上海联影医疗科技有限公司 | A kind of pet detector and medical imaging device |
| WO2021140233A2 (en) | 2020-01-10 | 2021-07-15 | Terapet Sa | Ion beam emission apparatus and detection system therefor |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US10908086B2 (en) * | 2018-12-26 | 2021-02-02 | Industrial Technology Research Institute | Signal processing system and method thereof |
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Also Published As
| Publication number | Publication date |
|---|---|
| TW201800776A (en) | 2018-01-01 |
| TWI599790B (en) | 2017-09-21 |
| CN107544086B (en) | 2020-03-10 |
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