CN106646582A - PET (Positron Emission Tomograph) detector and manufacturing method thereof - Google Patents
PET (Positron Emission Tomograph) detector and manufacturing method thereof Download PDFInfo
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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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- 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 application provides a PET (Positron Emission Tomograph) detector and a manufacturing method thereof. The PET detector comprises a scintillation crystal array, a detection unit and a signal processing circuit which are connected in sequence. The scintillation crystal array comprises multiple scintillation crystal units. Each scintillation crystal unit comprises a light entry surface, a light exit surface and a crystal side surface used for connecting the light entry surface and the light exit surface. The detection unit comprises multiple detection pixels. Each detection pixel is correspondingly connected with one scintillation crystal unit. The signal processing circuit connected with the connection unit is used for obtaining event information corresponding to Gamma photons according to electric signals. The crystal side surface of each scintillation crystal unit has an inclination angle, and the crystal side surface has a reflection layer used for reflecting light signals generated by the scintillation crystal unit. The light exit surface of each scintillation crystal unit is the same as and is aligned and coupled with the light entry surface used for receiving the light signals of the detection pixel. The pulse energy output by the detection pixels is enabled to be large, and the detection efficiency is improved.
Description
Technical field
The application is related to Medical Devices technology, more particularly to a kind of PET detector and preparation method thereof.
Background technology
PET (Positron Emission Tomograph, Positron emission computed tomography) detector be for
The device of the event information of collection positron annihilation events, for example, can gather the γ photons obtained in event information and be flashed
Position, time and the energy that triggered that crystal is received.PET detector can include：Scintillation crystal array, probe unit and
Signal processing circuit；Wherein, scintillation crystal array is used to receive γ photons and produce corresponding optical signal, with scintillation crystal array
The probe unit of connection for example can be SiPM or APD etc., for the corresponding optical signal of the γ photons to be converted to into telecommunications
Number, the signal processing circuit being connected with probe unit, the electric signal identification for being produced according to probe unit obtains event information.
Probe unit is an array structure being made up of many detected pixels, each detected pixel and scintillation crystal array
In a scintillation crystal unit correspond be connected, scintillation crystal unit produce optical signal can be input to detected pixel
In.But, there is gap between adjacent detected pixel, in prior art, have a big chunk optical signal and shine the seam
At gap, the loss for causing optical signal to export, and loss of optical signal will reduce the detection efficiency of detector；Even if can in correlation technique
To arrange reflective surface, the light that goes out at gap is reflexed in detected pixel, and the light signal energy after multiple reflections is significantly
Reduce, still cannot effectively improve the detection efficiency of detector.
The content of the invention
In view of this, the application provides a kind of PET detector and preparation method thereof, is imitated with the detection for improving PET detector
Rate.
Specifically, the application is achieved by the following technical solution：
First aspect, there is provided a kind of PET detector, the PET detector includes：The scintillation crystal array that is sequentially connected,
Probe unit and signal processing circuit；
The scintillation crystal array includes multiple scintillation crystal units, and the scintillation crystal unit includes：For receiving γ
The incidence surface of photon, for export γ photons triggering produce optical signal exiting surface and for connecting incidence surface and going out light
The crystal on side face in face；The probe unit includes the multiple detected pixels constituted with array；Each detected pixel with one
Scintillation crystal unit correspondence connects, for the optical signal that the scintillation crystal unit is exported to be converted to into electric signal；With the spy
The signal processing circuit of unit connection is surveyed, for obtaining the corresponding event information of γ photons according to electric signal identification；
The crystal on side face of the scintillation crystal unit has angle of inclination, and the crystal on side face with described for reflecting
The reflecting layer of the optical signal that scintillation crystal unit is produced；
It is used to receive the incidence surface size phase of optical signal in the exiting surface of the scintillation crystal unit, with the detected pixel
Same and alignment coupling.
Second aspect, there is provided a kind of preparation method of PET detector, methods described includes：
Scintillation crystal unit is made, the scintillation crystal unit includes：For receiving the incidence surface of γ photons, for exporting
The exiting surface and the crystal on side face for connecting incidence surface and exiting surface of the optical signal that the triggering of γ photons is produced；The crystal
Side has angle of inclination, and it is equivalently-sized with the incidence surface of detected pixel to arrange the exiting surface of scintillation crystal unit；
In the crystal on side face for making the scintillation crystal unit for obtaining, paste and produced for reflecting the scintillation crystal unit
The reflecting layer of raw optical signal；
Multiple scintillation crystal units are constituted into scintillation crystal array；
The gap between each adjacent detected pixel in filling probe unit；
By the exiting surface of the scintillation crystal unit, with the incidence surface for being used to receive optical signal in detected pixel coupling is directed at
Close；
Signal processing circuit is connected on the probe unit.
PET detector and preparation method thereof that the application is provided, by by the exiting surface of scintillation crystal unit be set to
It is equivalently-sized between the incidence surface of detected pixel so that the optical signal of crystal unit output is substantially all and can enter into detection
Pixel, will not shine again at the gap between detected pixel；Also, by the way that the crystal on side face of scintillation crystal unit is set to
Inclined side, and being sticked reflecting layer in the side, being capable of effective quick reflex optical signal so that optical signal is along crystal axis
Line direction is quickly conducted downwards in crystals, until entering into detected pixel；Therefore, the PET detector of the application can be with
So that the optical signal that scintillation crystal unit is produced, the overwhelming majority can enter into detected pixel, and then cause detected pixel defeated
The pulse energy for going out is larger, improves detection efficiency.
Description of the drawings
Fig. 1 is a kind of composition structure of the PET detector shown in the exemplary embodiment of the application one；
Fig. 2 is a kind of structural representation of the probe unit shown in the exemplary embodiment of the application one；
Fig. 3 is the connection knot between a kind of scintillation crystal array and probe unit shown in the exemplary embodiment of the application one
Structure；
Fig. 4 is a kind of reflection route map of the optical signal shown in the exemplary embodiment of the application one；
Fig. 5 is that a kind of angle of inclination of the crystal on side face shown in the exemplary embodiment of the application one determines schematic diagram；
Fig. 6 is that a kind of stop member shown in the exemplary embodiment of the application one arranges schematic diagram；
Fig. 7 is that another kind of stop member shown in the exemplary embodiment of the application one arranges schematic diagram；
Fig. 8 is a kind of Making programme of the PET detector shown in the exemplary embodiment of the application one；
Fig. 9 is the structural representation of the PET detector formed according to the flow process of Fig. 8；
Figure 10 is the operation principle schematic diagram of PET detector.
Specific embodiment
Here exemplary embodiment will be illustrated in detail, its example is illustrated in the accompanying drawings.Explained below is related to
During accompanying drawing, unless otherwise indicated, the same numbers in different accompanying drawings represent same or analogous key element.Following exemplary embodiment
Described in embodiment do not represent all embodiments consistent with the application.Conversely, they be only with it is such as appended
The example of the consistent apparatus and method of some aspects described in detail in claims, the application.
Fig. 1 shows three parts included by PET detector：Scintillation crystal array 11, probe unit 12 and letter
Number process circuit 13.
Wherein, scintillation crystal array 11 includes the multiple scintillation crystal units for arranging in the form of an array, and each flicker is brilliant
Body unit is used to receive the γ photons of positron annihilation events generation, and ionizes under the triggering of the γ photons, inspires
Optical signal.And the probe unit being connected with scintillation crystal array 11, for collecting the optical signal, and be converted to corresponding electric signal
That is pulse；For the optical signal of scintillation crystal unit output, unit reception, part optical signals might not be all detected
May lose, and energy size and the optical signal that it is received of the electric signal that probe unit is produced number it is relevant, reception
Optical signal is more, and the electrical signal energy of generation is bigger.The signal processing circuit being connected with probe unit, can be described by identification
The energy of electric signal come determine the electric signal produce whether this is indicate that have been received by positron annihilation events generation γ light
Son.
For simple example, it is assumed that after a γ photon strikes to scintillation crystal unit, the crystal unit produces 3000
Individual light photon, and if these light photons are all detected after unit reception, probe unit is according to visible ray light
The energy of the electric pulse that son is converted into is sufficiently high, and signal processing circuit have received by recognizing that the size of the energy can determine that
γ photons；And if having lost a big chunk light photon, only 1000 light photons are detected unit and receive, that
The energy of the electric pulse that probe unit is produced is relatively low, and the energy that signal processing circuit recognizes the electric pulse is little and be judged to not connect
Receive γ photons.It can be seen that, the transmitting of the optical signal between scintillation crystal array and probe unit is extremely important, directly affects
To the generation that whether can fast and accurately detect positron annihilation events, if it is possible to ensure enough optical signal transmissions
To probe unit, then can aid in PET detector and fast and accurately detect γ photons, that is, improve detection efficiency.
The structure of the probe unit 12 in the application may refer to shown in Fig. 2, and the probe unit 12 can be included with array
Multiple detected pixels of formula composition, for example, detected pixel 121, detected pixel 122 in Fig. 2 etc..Each detected pixel includes
One effective sensitive surface 123, the optical signal of scintillation crystal unit output can enter into detected pixel by effective sensitive surface 123
In, for being converted to electric signal.Between effective sensitive surface of adjacent detected pixel, the gap being properly termed as between detected pixel
124, the gap 124 can not receive optical signal, it is possible to use the glue with certain cementability and mobility is filled at the gap.
Exemplary, the probe unit of the application can be：The SiPM arrays being made up of multiple SiPM pixels.
Fig. 3 illustrates the attachment structure between scintillation crystal array and probe unit, as shown in figure 3, scintillation crystal array
Scintillation crystal unit and the detected pixel of probe unit between, using the structure that connects one to one.For example, scintillation crystal
Corresponding connection between unit 31 and detected pixel 32, corresponding connection between scintillation crystal unit 33 and detected pixel 34.
Each scintillation crystal unit can include：Incidence surface 35, exiting surface 36 and for connecting incidence surface and exiting surface
Crystal on side face 37, wherein, incidence surface 35 is used to receive γ photons, and exiting surface 36 is used to export the light letter that the triggering of γ photons is produced
Number, in this example, crystal on side face 37 has angle of inclination, such as Fig. 3 examples, and crystal on side face enters light with scintillation crystal unit
The angle in face 35 is at an acute angle, with the angle of the exiting surface 36 of scintillation crystal unit into obtuse angle.Also, crystal on side face 37 can be sticked
There is reflecting layer 38, the reflecting layer 38 can be used for reflecting the optical signal that scintillation crystal unit is produced.
Additionally, can further be seen that the optical signal of the exiting surface output of scintillation crystal unit, entering by detected pixel by Fig. 3
Light face enters pixel, and the incidence surface of the detected pixel is equivalently-sized with the exiting surface of scintillation crystal unit and is directed at coupling.Example
Such as, the exiting surface 39 of the scintillation crystal unit 33 of Fig. 3 examples, it is equivalently-sized and right and the incidence surface 40 of detected pixel 34 between
It is accurate.
Using the structure shown in above-mentioned Fig. 3, when scintillation crystal unit receives the γ light period of the day from 11 p.m. to 1 a.m, for crystal unit is inspired
Optical signal, can effectively conduct to correspondence connection detected pixel.For example, with the scintillation crystal unit 33 in Fig. 4 and spy
As a example by surveying pixel 34, the reflecting layer 38 attached using the crystal on side face of scintillation crystal unit 33 can quickly by crystal unit
The optical signal for exciting is reflexed at exiting surface, and is input in pixel by the incidence surface of detected pixel.
The PET detector structure of this example, on the one hand, due to exiting surface and the detected pixel 34 of scintillation crystal unit 33
It is equivalently-sized between incidence surface, so the optical signal of crystal unit output is substantially all and can enter into detected pixel, will not
Shine again at the gap between detected pixel；On the other hand, by being set to the crystal on side face of scintillation crystal unit to incline
Side, and be sticked reflecting layer in the side, being capable of effective quick reflex optical signal so that optical signal is along crystal axis side
To quickly conducting downwards in crystals, until entering into detected pixel.Above-mentioned 2 points, relative to existing structure, can make
The optical signal that scintillation crystal unit is produced is obtained, the overwhelming majority can enter into detected pixel, and then cause detected pixel output
Pulse energy it is larger, improve detection efficiency.
Loss caused by transmiting for the crystal on side face for reducing optical signals scintillation crystal unit, can be by crystal on side face
The reflectance factor in the reflecting layer of setting is more than 98%, and the optical signal of the overwhelming majority can be so effectively ensured all in scintillation crystal list
Reflected in unit, until by the exiting surface outgoing of crystal unit, reducing transmission.
Additionally, the angle of inclination of the crystal on side face of scintillation crystal unit, the present embodiment is not limited, such as, and two crystal
The angle of inclination of side can be with identical, or can also be different.It is at an acute angle with the incidence surface of scintillation crystal unit with crystal on side face,
With the exiting surface of scintillation crystal unit into as a example by obtuse angle, the inclination angle design of crystal on side face is illustrated with reference to Fig. 5：Assume scintillation crystal
The incidence surface size of unit is 4.13mm, and exiting surface size is 3mm, with the incidence surface of detected pixel (i.e. effective sensitive surface) size
It is identical, it is 3mm, the height of scintillation crystal unit is 20mm.Also set up the inclination of two crystal on side face of scintillation crystal unit
Angle is consistent, such as the example of Fig. 5, the angle between the incidence surface of scintillation crystal unit and two crystal on side face is all a.According to
Above-mentioned size, can calculate the inclination angle of crystal on side face：Tan a=20mm/ [(4.13-3) mm/2], obtain accordingly the numerical value of a,
And the angle b=90-a+90 between the exiting surface of scintillation crystal unit and two crystal on side face.For example, can through above-mentioned calculating
To determine, angle a is 86.8 degree, and angle b is 93.2 degree.
In another example, when there are positron annihilation events, if the γ photons that event is produced sideling inject sudden strain of a muscle
Bright crystal unit, may occur crosstalk between scintillation crystal unit, as shown in fig. 6, original γ photons are actually by flashing
Crystal unit 31 is received, but the γ photons traverse to adjacent scintillation crystal unit 33, excites scintillation crystal unit 33 to produce
Corresponding optical signal, so when follow-up signal process circuit is recognized, it is possible to be identified as scintillation crystal unit 33 and receive γ
Photon.In order to avoid crosstalk phenomenon between above-mentioned crystal as far as possible, this example in PET detector, in the phase of scintillation crystal array
Between adjacent scintillation crystal unit, the stop member for preventing the crosstalk between crystal of γ photons is also provided with, the stop member tool
Have higher for the absorbability of γ photons, when γ photons will traverse to neighbouring crystal unit, crystalline substance will be arranged on
The stop member between body is absorbed, so as to effectively prevent crystal crosstalk.
Continuing with referring to Fig. 6, stop member can be a thin layer catch 61, and the thin layer catch 61 for example can be tungsten gear
The material such as piece or lead catch, and the height of the thin layer catch 61 can be highly consistent with scintillation crystal unit.Or,
Stop member can also be arranged to the triangular prism 62 of Fig. 7 examples, and the shape of triangular prism 62 is with the crystalline substance of adjacent scintillation crystal unit
Gap between body side surface is defined.The material of triangular prism 62 can be identical with the material of thin layer catch 61.
Even if additionally, have sub-fraction γ photon still can enter into another scintillation crystal list through stop member
Unit, due to the inhibition of stop member so that entering into the energy of the γ photons of another crystal unit quickly reduces, so as to quilt
The corresponding signal processing circuit of another crystal unit is abandoned by Thin interbed, it is also possible to avoided for γ photon acceptors position
The error in judgement put.
The PET detector of this example, by being provided with stop member between scintillation crystal unit, can effectively hinder γ
Photon traverses to neighbouring crystal unit such that it is able to improve the spatial resolution of system, you can accurately to recognize γ light
The receiving position of son.Further, since the detection efficiency and spatial resolution of PET detector are all improved, enabling more
Higher-quality reconstruction image is obtained in the short time, the sweep time of patient is reduced, the circulation of patient is improve.
Fig. 8 illustrates the Making programme of the PET detector of the application, to make SiPM detectors as a example by, i.e., in this example
The probe unit, including：The SiPM arrays being made up of multiple SiPM pixels.
In step 801, scintillation crystal unit is made, the scintillation crystal unit includes：For receiving entering for γ photons
Light face, the exiting surface for exporting the optical signal that the triggering of γ photons is produced and the crystal for connecting incidence surface and exiting surface
Side；The crystal on side face has angle of inclination, and arranges the exiting surface of scintillation crystal unit and the incidence surface chi of detected pixel
It is very little identical.
In this step, when scintillation crystal unit is made, the scintillator crystal materials for using can be：In BGO, LSO, LYSO
One or more.Crystal on side face can be configured with the side at angle of inclination, for example, can be by crystal on side face and flicker
The incidence surface of crystal unit arranges at an acute angle, and with the exiting surface of scintillation crystal unit obtuse angle is arranged to.Also, by scintillation crystal list
The size of the exiting surface of unit, is arranged to equivalently-sized with the incidence surface of detected pixel, is the area of 3*3 for example.Additionally, should
Scintillation crystal unit also includes the incidence surface for receiving γ photons.
In step 802, in the crystal on side face for making the scintillation crystal unit for obtaining, paste brilliant for reflecting the flicker
The reflecting layer of the optical signal that body unit is produced.
For example, the reflector material that this step is used, can include：BaSo4 or 3M reflectance coatings, and it is possible to make
With the higher material of reflectance factor.
In step 803, multiple scintillation crystal units are constituted into scintillation crystal array.
Multiple scintillation crystal units are constituted scintillation crystal array by this step.
In another example, in order to improve spatial resolution, crosstalk between the crystal of γ photons is prevented, may be used also in this step
Between adjacent scintillation crystal unit, to be provided for preventing the stop member of γ photons crosstalk between crystal, this example with
As a example by thin layer catch, a thin layer catch is all set between each two scintillation crystal unit, and with optical cement to scintillation crystal
Unit and thin layer catch do bonding.
In step 804, the gap between each the adjacent detected pixel in probe unit is filled.
This step carries out the making of probe unit, is made up of in the form of an array multiple detected pixels；For adjacent detection
Gap between pixel, can be filled in the gap of SiPM with the glue with certain cementability and mobility, and by SiPM battle arrays
Row are placed at plane, it is ensured that the flatness of glue-line.
In step 805, by the probe unit behind gap between filling detected pixel, carry out the row's bubble at gap and process.
For example, the SiPM arrays after filling glue can be placed in row's bulb apparatus, be completed to the row at SiPM arrays gap
Bubble, it is ensured that bubble-free in glue-line, prevents from causing the scattering loss of visible ray because there is bubble.
In step 806, will be used to receive the incidence surface of optical signal in the exiting surface of scintillation crystal unit, with detected pixel
Alignment coupling.
This step by optical coupled dose of the surface smear of scintillation crystal array, and can be coupled, coupling with the incidence surface of SiPM
Need to be directed at relative fiducial positions by frock during conjunction.
In this example, the relative scintillation crystal array for connecing can be N*M arrays, and SiPM arrays can be m*n arrays, wherein
N, M, m, n can be integer arbitrarily more than 1, and N*M and m*n can be with inconsistent, as long as ensureing detected pixel with flicker crystalline substance
Body unit connects one to one.
In step 807, PET detector is stood, to treat curable adhesive layer.
For example, the PET detector after coupling can be placed in the standing case with temperature and humidity control and stands one section
Time, treat curable adhesive layer.
In step 808, signal processing circuit is connected on the probe unit.
For example, this step can be welded on signal processing circuit board on SiPM arrays, complete the circuit weldering of PET detector
Connect.
After the flow process shown in Fig. 8, the structure of the PET detector of formation can be as shown in Figure 9.
The PET detector that above-mentioned making is formed, the signal of its operation principle such as Figure 10, at the signal being connected with SiPM arrays
Reason circuit, can include：The threshold decision circuit of energy information reading circuit, temporal information reading circuit and energy；Wherein,
Energy information reading circuit can carry out the collection of energy by the electric signal exported to SiPM, and threshold decision circuit can lead to
Cross threshold value to be identified energy, if energy reaches threshold value, show that this is the data of validity event, otherwise, if telecommunications
Number energy it is relatively low, then it is assumed that be the data of invalid event.For the data of validity event, in conjunction with temporal information reading circuit
The event time of demarcation, obtains the event based on the temporal information of TOF and positional information occurs.It can be seen that, by connecting with probe unit
The signal processing circuit for connecing, can obtain the corresponding event information of γ photons, including energy, time, position according to electric signal identification
The information such as put.
The PET detector preparation method provided by the application, can obtain having the PET of higher detection efficiency to detect
Device, and also during using the PET detector, can faster obtain higher-quality with the spatial resolution of lift system
Reconstruction image.
The preferred embodiment of the application is the foregoing is only, not to limit the application, all essences in the application
Within god and principle, any modification, equivalent substitution and improvements done etc. should be included within the scope of the application protection.
Claims (10)
1. a kind of PET detector, it is characterised in that the PET detector includes：Scintillation crystal array, the detection being sequentially connected
Unit and signal processing circuit；
The scintillation crystal array includes multiple scintillation crystal units, and the scintillation crystal unit includes：For receiving γ photons
Incidence surface, the exiting surface for exporting the optical signal that the triggering of γ photons is produced and for connecting incidence surface and exiting surface
Crystal on side face；The probe unit includes the multiple detected pixels constituted with array；Each detected pixel and a flicker
Crystal unit correspondence connects, for the optical signal that the scintillation crystal unit is exported to be converted to into electric signal；It is single with the detection
The signal processing circuit of unit's connection, for obtaining the corresponding event information of γ photons according to electric signal identification；
The crystal on side face of the scintillation crystal unit has angle of inclination, and the crystal on side face has for reflecting the flicker
The reflecting layer of the optical signal that crystal unit is produced；
In the exiting surface of the scintillation crystal unit, with the detected pixel be used for receive optical signal incidence surface it is equivalently-sized and
Alignment coupling.
2. PET detector according to claim 1, it is characterised in that the crystal on side face and the scintillation crystal unit
Incidence surface it is at an acute angle, with the exiting surface of scintillation crystal unit into obtuse angle.
3. PET detector according to claim 1 and 2, it is characterised in that the adjacent flicker of the scintillation crystal array is brilliant
Between body unit, arrange：For preventing the stop member of γ photons crosstalk between crystal.
4. PET detector according to claim 3, it is characterised in that the stop member, including：Catch or Rhizoma Sparganii
Post.
5. PET detector according to claim 4, it is characterised in that
The material of the stop member includes：Tungsten or lead；
The reflector material, including：BaSo4 or 3M reflectance coatings.
6. PET detector according to claim 1, it is characterised in that the probe unit, including：By multiple SiPM pictures
The SiPM arrays of element composition.
7. a kind of preparation method of PET detector, it is characterised in that methods described includes：
Scintillation crystal unit is made, the scintillation crystal unit includes：For receiving the incidence surface of γ photons, for exporting γ light
The exiting surface and the crystal on side face for connecting incidence surface and exiting surface of the optical signal that son triggering is produced；The crystal on side face
With angle of inclination, and it is equivalently-sized with the incidence surface of detected pixel to arrange the exiting surface of scintillation crystal unit；
In the crystal on side face for making the scintillation crystal unit for obtaining, paste for reflecting what the scintillation crystal unit was produced
The reflecting layer of optical signal；
Multiple scintillation crystal units are constituted into scintillation crystal array；
The gap between each adjacent detected pixel in filling probe unit；
By the exiting surface of the scintillation crystal unit, with the incidence surface for being used to receive optical signal in detected pixel coupling is directed at；
Signal processing circuit is connected on the probe unit.
8. method according to claim 7, it is characterised in that the crystal on side face enters light with the scintillation crystal unit
Face is at an acute angle, with the exiting surface of scintillation crystal unit into obtuse angle.
9. method according to claim 7, it is characterised in that described that multiple scintillation crystal units are constituted into scintillation crystal battle array
Row, also include：
To be used to prevent the stop member of γ photons crosstalk between crystal, be arranged between adjacent scintillation crystal unit.
10. method according to claim 7, it is characterised in that methods described also includes：
By the probe unit behind gap between filling detected pixel, carry out the row's bubble at gap and process.
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| CN108852391A (en) * | 2017-05-15 | 2018-11-23 | 通用电气公司 | The system and method for collimation sensitivity for raising |
| CN109765599A (en) * | 2018-12-11 | 2019-05-17 | 东软医疗系统股份有限公司 | Detector, rack and PET device based on silicon photomultiplier |
| CN110376634A (en) * | 2019-07-19 | 2019-10-25 | 东软医疗系统股份有限公司 | Probe unit and pet detector for 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 |
| CN111638543A (en) * | 2020-05-28 | 2020-09-08 | 中国科学院近代物理研究所 | Manufacturing process of position-sensitive crystal array probe |
| CN112114347A (en) * | 2019-06-21 | 2020-12-22 | 清华大学 | Apparatus and method for manufacturing scintillator detector |
| WO2024023679A1 (en) * | 2022-07-26 | 2024-02-01 | Consiglio Nazionale Delle Ricerche | Measuring structure for pet and spect applications |
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| CN109765599A (en) * | 2018-12-11 | 2019-05-17 | 东软医疗系统股份有限公司 | Detector, rack and PET device based on silicon photomultiplier |
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| CN112114347A (en) * | 2019-06-21 | 2020-12-22 | 清华大学 | Apparatus and method for manufacturing scintillator detector |
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| CN110376634A (en) * | 2019-07-19 | 2019-10-25 | 东软医疗系统股份有限公司 | Probe unit and pet detector for 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 |
| CN110426730B (en) * | 2019-07-19 | 2022-11-01 | 东软医疗系统股份有限公司 | Signal reading circuit, signal reading method and device |
| CN111638543A (en) * | 2020-05-28 | 2020-09-08 | 中国科学院近代物理研究所 | Manufacturing process of position-sensitive crystal array probe |
| CN111638543B (en) * | 2020-05-28 | 2021-07-13 | 中国科学院近代物理研究所 | Manufacturing process of position-sensitive crystal array probe |
| WO2024023679A1 (en) * | 2022-07-26 | 2024-02-01 | Consiglio Nazionale Delle Ricerche | Measuring structure for pet and spect applications |
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Address after: 110167 No. 177-1 Innovation Road, Hunnan District, Shenyang City, Liaoning Province Applicant after: DongSoft Medical System Co., Ltd. Address before: Hunnan New Century Road 110179 Shenyang city of Liaoning Province, No. 16 Applicant before: Dongruan Medical Systems Co., Ltd., Shenyang |
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Application publication date: 20170510 |