CN107320121A - Positron emission tomography photon detection device - Google Patents
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- CN107320121A CN107320121A CN201610279904.1A CN201610279904A CN107320121A CN 107320121 A CN107320121 A CN 107320121A CN 201610279904 A CN201610279904 A CN 201610279904A CN 107320121 A CN107320121 A CN 107320121A
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- 238000002600 positron emission tomography Methods 0.000 title claims abstract description 11
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
- G01T1/2914—Measurement of spatial distribution of radiation
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/037—Emission tomography
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/202—Measuring radiation intensity with scintillation detectors the detector being a crystal
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Abstract
The invention discloses a kind of positron emission tomography photon detection device, including the detection array being made up of multiple probe units, the probe unit includes at least one scintillation component, and at least one electrooptical device is coupled in each scintillation component, each electrooptical device is connected to the energy signal reading circuit and time signal read circuit of detection event.Photon detection device provided by the present invention, with time detection accuracy is preferable and lower-cost advantage.
Description
【Technical field】
It is used for positron emission the present invention relates to positron emission tomography field, more particularly to one kind
The photon detection device of fault imaging.
【Background technology】
As PET (Positron Emission Tomography, positron emission computerized tomography) is imaged
The development of technology, PET scan equipment has been widely used in medical field.PET scan equipment is
A kind of advanced medical diagnosis imaging device, it has also become in tumour, the heart, cerebral disease diagnosis and pathological study not
The visual plant that can lack.In PET scan, first to patient's injection of radioactive substances, the radioactivity
Medicine is showing as the compound synthesis needed for the body metabolisms such as radionuclide and glucose, choline, acetic acid
Track agent, these radionuclides convert protons to neutron, and discharge positive electron and neutrin.Positive electron
Quality it is equal with electronics, the electricity of positive electron is identical with the electricity of electronics, and simply symbol is opposite.It is this just
Electronics is run after very short distance in tissue, i.e., with the electron interaction in ambient substance, fall into oblivion
Go out radiation, launch in opposite direction, two photons of energy equal (511keV), to these high-penetrations
Photon carry out meeting detection, and constituted with the position of the method reconstruction annihilation event generation of analysis or statistics
PET basis.
TOF (Time Of Flight, flight time) technology is applied on PET, is to conventional PET
The further improvement of imaging technique.Because the transmission of photon is carried out with the light velocity, what positive electron was buried in oblivion
Position is different, then the photon produced by same annihilation event is different, TOF to the time for reaching detector
Technology reaches the time difference of detector rings by measuring two photons of photon pair, can be estimated according to the light velocity
Annihilation event is radiated by meeting the approximate location met determined by detection on line therefore, it is possible to directly determination
Property nucleic (tracer) distribution in internal organs, tissue, hence it is evident that collection sensitivity and image resolution ratio is provided.
PET photon detection device includes PET front-end circuits.In known technology：PET front-end circuits are to make
Photon is detected with PMT (PhotoMultiplier Tube, photomultiplier) arrays and reaches detector
The fluorescence of crystal (scintillator), and the decoding of annihilation event is carried out, but because PMT power supply is needed to use
High pressure, and each PMT is installed and safeguarded as single individual so that PET less stable
And install complicated；The PET front-end circuits of newer type be based on SIPM (Silicon Photomultipliers,
Silicon photomultiplier) array carrys out the fluorescence of crystal detection, and each SIPM is individually coupled with a crystal, is come
The generation of annihilation event is recorded, so when detector crystal quantity is more, corresponding SIPM usage quantities will
Increase therewith, and back-end circuit needs the signal handled to be consequently increased, and causes the scale of back-end circuit very
It is huge；Size additionally, due to SIPM limits the size of detector crystal, causes the size of crystal can not
Arbitrarily change；Follow-on PET front-end circuits are come the fluorescence of crystal detection, every four based on SIPM arrays
Individual SIPM is coupled with a crystal Block, but be due to SIPM die-away time it is longer, signal is slower,
Cause the dead time of whole front-end circuit long, cause TOF performances (time detection accuracy) not good.
Therefore, it is necessary to provide, a kind of new time detection accuracy is preferable and lower-cost photon detection dress
Put.
【The content of the invention】
What the present invention was solved is existing positron emission tomography photon detection setup time detection accuracy
Not good the problem of.
To solve the above problems, the present invention proposes that a kind of photon detection for positron emission tomography is filled
Put, including the detection array being made up of multiple probe units, the probe unit includes at least one scintillator,
And at least one electrooptical device is coupled in each scintillator, each electrooptical device connection
There are the energy signal reading circuit and time signal read circuit of detection event.
In one embodiment of the present invention, the electrooptical device for being coupled in same scintillator is connected to together
One time signal read circuit.
In one embodiment of the present invention, in the probe unit, 4 electrooptical devices are coupled in
Same scintillator.
In one embodiment of the present invention, the scintillator is cube, 4 electrooptical device couplings
Together in the same face of the scintillator.
In one embodiment of the present invention, the energy signal reading circuit includes row signal read-out channel and row
Signal read-out channel, the row, column information of energy signal is read by the passage respectively, determines the detection thing
Positional information of the part in the detection array.
In one embodiment of the present invention, the energy signal reading circuit includes the first differential circuit, leads to
First differential circuit is crossed to sum to each row, column signal, decode to obtain the positional information.
In one embodiment of the present invention, the time signal reading circuit includes the second differential circuit, leads to
Second differential circuit is crossed to believe the time of the electrooptical device for being coupled in same scintillator
Number accelerated.
In one embodiment of the present invention, the electrooptical device is SIPM devices.
In one embodiment of the present invention, the scintillator is LYSO crystal.
The present invention has following beneficial effect compared with prior art：The energy information of the event of detection is believed with the time
Breath separately processing so that script rising edge is slow, the signal of die-away time length becomes quickly, to greatly reduce spy
The accumulation of survey event so that detection device still possesses preferable time precision in the case where height is counted, and improves spy
Survey the TOF performances of device.
【Brief description of the drawings】
Fig. 1 is positron emission tomography photon detection apparatus structure schematic diagram；
Fig. 2 is the scintillator arrays schematic diagram of one embodiment of the invention；
Fig. 3 is the detection array structural representation of one embodiment of the invention；
Fig. 4 is the energy signal reading circuit structure schematic diagram of one embodiment of the invention；
Fig. 5 is the time signal reading circuit structure schematic diagram of one embodiment of the invention.
【Embodiment】
In order to facilitate the understanding of the purposes, features and advantages of the present invention, it is right below in conjunction with the accompanying drawings
The embodiment of the present invention is described in detail.
Fig. 1 is positron emission tomography photon detection apparatus structure schematic diagram, is retouched as illustrated examples
State, in positron emission computerized tomography (PET), radiopharmaceutical is injected into imaging object, its radioactivity
Decay event produces positive electron.Each positive electron is with electron interaction to produce the gamma of two phase opposite senses
(γ) photon.The gammaphoton is detected device detecting and is carried out meeting verification by system, and is responded
Line is counted with reconstruction image.Photon detection device proposed by the present invention for positron emission tomography,
Include the detection array being made up of multiple probe units 100.As shown in figure 1, detection array annular cloth
It is placed in around checked object, will after the probe unit for constituting detection array detects photo-event 200
The energy information of detection photon, temporal information, positional information are collected, changed and after reponse system progress
Continuous processing.
Probe unit 100 can be coupled with electrooptical device by scintillation component and constituted, when gammaphoton enters
After detector, if interacted with scintillation component, fluorescence will be produced, fluorescence is turned by photoelectricity
Parallel operation part is changed into electric signal (multiplication amplification).Scintillation component can be by scintillation crystal or scintillation crystal array
Composition.According to one embodiment of present invention, as shown in Fig. 2 scintillation component 101 is by scintillation crystal battle array
Row composition, the array is usually, multiple scintillation crystals, to be glued by additional reflecting layer, and by optical glue
Knot assembles.Ordinary circumstance, single scintillation crystal is designed as the cuboid of rule.In order to by itself and light
Electrical switching device is combined, it is necessary to a surface of scintillation crystal array is made opposed flattened, by grinding plus
Work is optical coupled with electrooptical device to carry out.In terms of material, scintillation crystal array can be BGO (germanium
Sour bismuth) crystal array or LYSO (yttrium luetcium silicate) crystal arrays or LSO (silicic acid lutetium) crystal array
Deng.Electrooptical device can be PMT (photomultiplier), APD (avalanche photodide) or SIPM
(silicon photomultiplier).Wherein, LYSO scintillation crystals have High Light Output, rapid decay time, visited
Efficiency high, the low feature of cost are surveyed, SIPM has high-gain, low work compared to other electrooptical devices
The features such as voltage, strong antijamming capability, combination can be used as a kind of preferred embodiment of the invention.
Such as Fig. 3 (a), shown in (b), according to one embodiment of present invention, detection array it is every
One probe unit is coupling in the same of scintillation component by 4 electrooptical devices (such as SIPM)
(can be LYSO scintillation crystal arrays) be constituted in burnishing surface, according to the change case of the embodiment, also can be
The electrooptical device of other quantity couples same scintillation component, for example, choosing 9:1、16：1 grade ratio
Example is coupled etc., also can be N:1 ratio is coupled, wherein N=a × b, a, and b is the flicker
The line number and columns of monocrystalline scapus in crystal array, shown in such as Fig. 3 (c).In identical scintillation component
Under the premise of size, electrooptical device with scintillation component is more a high proportion of couples, be more conducive to improving and detect
The sensitivity of device, makes its anti-bulk property better.
After photo-event is detected, the electric signal that the electrooptical device of probe unit is produced can be used for determining
Photon energy (energy signal, i.e. anode signal) information and Time To Event information (time signal, i.e.,
Fast signal), and determine to produce positional information of the electrooptical device of electric signal in detection matrix.Energy
The characteristics of measuring signal is that signal amplitude is larger, but is read slower.The characteristics of time signal is that signal amplitude is small,
But read very fast.According to this difference, each electrooptical device is connected to detection by the present invention
The energy signal reading circuit and time signal read circuit of event, with realize by energy (position) signal with
Time signal is independently read, and improves the time precision of detection device.
Fig. 4 is the structural representation of energy signal reading circuit middle according to one embodiment of present invention.Detect thing
The energy signal reading circuit of part is anode signal reading circuit, and it is used to determine that electrooptical device is detected
Photon energy size, further, each electrooptical device in detection array (is such as coupled in same
SIPM 102a, 102b, 102c and 102d of scintillation component), it is respectively connected with row signal read circuit
And column signal reading circuit, include row differential circuit (differential adder 103 respectively per a line reading circuit
And ADC signal switching device 105), each row reading circuit includes row differential circuit respectively, and (differential adds
Musical instruments used in a Buddhist or Taoist mass 104 and ADC signal switching device 106), by the row, column differential circuit to each row, column
Signal carries out differential summation and signal conversion, and is solved by decoding unit 107 (Decoding units)
The operation such as code and calculating, can also obtain the detection event in detection matrix while energy signal is obtained
Positional information.
Fig. 5 is the structural representation of time signal reading circuit middle according to one embodiment of present invention.It is real herein
Apply in example, according to the characteristics of time signal amplitude is small, reading is fast, would be coupled to the institute of same scintillation component
State electrooptical device and be connected to same time signal reading circuit (as being coupled in same scintillation component
SIPM 102a, 102b, 102c and 102d, it shares same time signal reading circuit), and further
Differential circuit (differentiation element 108) has been independently connected in ground, each time signal reading circuit, by this
Differential circuit is accelerated to the time signal of the electrooptical device for being coupled in same scintillator,
After comparator 109 produces trigger signal, trigger signal is transferred to the (time figure of TDC units 110
Converter, Time-to-Digital Converter), calculate the event occurred in the scintillation component
Temporal information.
The present invention is poor in the energy signal of electrooptical device and the electronics of time signal according to detection event
It is different, separately design mutual independent energy signal reading circuit for each electrooptical device and the time believes
Number reading circuit, and by the addition of differential circuit, improve the time precision and TOF of whole detection device
Performance.
Although the present invention disclosed as above with preferred embodiment, its be not for limiting the present invention, it is any
Those skilled in the art without departing from the spirit and scope of the present invention, the method that may be by the disclosure above
Possible variation and modification are made to technical solution of the present invention with technology contents, it is therefore, every without departing from this hair
The content of bright technical scheme, what the technical spirit according to the present invention was made to above example any simply repaiies
Change, equivalent variations and modification, belong to the protection domain of technical solution of the present invention.
Claims (9)
1. a kind of positron emission tomography photon detection device, including be made up of multiple probe units
Detection array, it is characterised in that：The probe unit includes at least one scintillation component, and
At least one electrooptical device is coupled in each scintillation component, each opto-electronic conversion
Device is connected to the energy signal reading circuit and time signal read circuit of detection event.
2. photon detection device according to claim 1, it is characterised in that be coupled in same institute
The electrooptical device of scintillation component is stated, same time signal reading circuit is connected to.
3. photon detection device according to claim 1, it is characterised in that the probe unit
In, 4 electrooptical devices are coupled in same scintillation component.
4. photon detection device according to claim 3, it is characterised in that the scintillator device
Part is the crystal array that some scintillation crystal posts are constituted, and the crystal array has at least one smooth
Face, 4 electrooptical devices are coupled in the burnishing surface of the scintillation component.
5. photon detection device according to claim 1 or 2, it is characterised in that the energy
Signal read circuit includes row signal read-out channel and column signal read-out channel, is distinguished by the passage
The row, column information of energy signal is read, position of the detection event in the detection array is determined
Confidence ceases.
6. photon detection device according to claim 5, it is characterised in that the energy signal
Reading circuit includes the first differential circuit, and each row, column is believed by first differential circuit
Number summed, decode to obtain the positional information.
7. photon detection device according to claim 1 or 2, it is characterised in that the time
Signal read circuit includes the second differential circuit, by second differential circuit to the coupling
Accelerated in the time signal of the electrooptical device of same scintillator.
8. photon detection device according to claim 1, it is characterised in that the opto-electronic conversion
Device is SIPM devices.
9. photon detection device according to claim 4, it is characterised in that the scintillation crystal
Post is LYSO crystal.
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Cited By (9)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN108181331A (en) * | 2017-12-20 | 2018-06-19 | 上海联影医疗科技有限公司 | A kind of signal detection circuit and detector |
| CN108294771A (en) * | 2018-01-02 | 2018-07-20 | 沈阳东软医疗系统有限公司 | A kind of Positron Emission Computed Tomography detector assembly |
| CN108535770A (en) * | 2018-05-09 | 2018-09-14 | 同方威视技术股份有限公司 | Twilight sunset detection device and twilight sunset detection method |
| CN109459783A (en) * | 2018-09-30 | 2019-03-12 | 中派科技（深圳）有限责任公司 | PET device, multilayer crystalline PET detector and its electronics read module and method |
| CN109991651A (en) * | 2017-12-29 | 2019-07-09 | 苏州瑞派宁科技有限公司 | A kind of measuring device and measuring method of PET system spatial resolution |
| CN110368014A (en) * | 2019-07-19 | 2019-10-25 | 东软医疗系统股份有限公司 | For the crystal array of pet detector, detector rings and pet detector |
| CN110426730A (en) * | 2019-07-19 | 2019-11-08 | 东软医疗系统股份有限公司 | Signal read circuit, signal reading method and device |
| CN113069138A (en) * | 2021-03-23 | 2021-07-06 | 上海联影医疗科技股份有限公司 | Positron emission tomography device, coincidence efficiency detection method and normalization method |
| CN113786209A (en) * | 2021-09-16 | 2021-12-14 | 华中科技大学 | Polyhedral brain PET system with ultrahigh sensitivity |
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