CN206671574U - A kind of nuclear medical imaging device SPECT/CT ray detector - Google Patents
A kind of nuclear medical imaging device SPECT/CT ray detector Download PDFInfo
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- CN206671574U CN206671574U CN201720443746.9U CN201720443746U CN206671574U CN 206671574 U CN206671574 U CN 206671574U CN 201720443746 U CN201720443746 U CN 201720443746U CN 206671574 U CN206671574 U CN 206671574U
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Abstract
The utility model belongs to technical field of medical equipment, is related to a kind of nuclear medical imaging device SPECT/CT ray detector, is provided with gamma-rays pipe；Multiple cone-beam lead holes are provided with the gamma-rays pipe；Photodiode is inlaid with inside gamma-rays pipe；The emergent light end of photodiode is contained in cone-beam lead hole；The lower end in cone-beam lead hole is spaced for will incide ray and be converted to the ray conversion layer of visible ray；Also there is the photodiode glass with globoidal structure to sink to the bottom layer successively；Photoelectric conversion layer；Pel array layer；Layer of lead glass；Read data circuit flaggy.The sensitivity of the utility model ray detector is very high, and external signal processing system can be allowed more easily to detect charge signal, so as to carry out X-ray detection X with the relatively low radiographic source of energy；So that the use cost of ray detector is relatively low, and be advantageous to save the energy.
Description
Technical field
The utility model belongs to technical field of medical equipment, more particularly to a kind of nuclear medical imaging device SPECT/CT is penetrated
Line detector.
Background technology
At present, ray detector has a wide range of applications in field in medical science, industrial production and manufacture etc., such as available for
Physical examination, workpiece flaw detection etc..Modern X-ray detection X technology has been able to be converted to ray signal to be detected can be straight
Connect the image or photo being shown on screen.
Gamma-rays pipe is widely used in the radiation imaging system in the fields such as medical science, material science and industrial nondestructive testing
In.Focal spot size is an important parameter of gamma-rays pipe, and it significantly affects the picture quality of radiation imaging system, gamma-rays pipe
Focal spot size is one of principal element for determining radiation imaging system limit space resolution ratio.In addition, along with gamma-rays pipe
Using, anode target surface, which becomes, can obtain coarse and then generation ray diffusing reflection, and cathode filament be because aging can change shape, both
The change of focal spot size will be caused to a certain extent, therefore the old of gamma-rays pipe can be assessed by the change of focal spot size
Change degree.In summary, focal spot size is the deciding factor of radiation imaging system spatial resolution, and can be used as weighing ray
The important evidence of pipe degree of aging and working condition, it is necessary to find suitable method and surveyed to the focal spot size of gamma-rays pipe
Amount.
In commercial Application, for conventional gamma-rays pipe, existing focus measuring method mainly has scanning method, pin hole method, narrow
Stitch and boundary method.4 kinds of methods of the above have the characteristics of respective, but the specific test work of special preparation is both needed in experiment measures
Tool.For example, scanning method needs a set of collimation and scanning system and scintillator count device, pin hole method need to make smaller than focal spot size one
The pinhole plate of magnitude, Narrow slit need to make extremely narrow slit plate, and boundary rule need to process the cylinder steel pipe that outer surface is covered by lead.
Above several method has to test condition compared with strict requirements, especially to gamma-rays pipe, testing tool and detector simultaneously
Status requirement is strict.In addition, certain methods are not simple in practical operation, such as scanning method is needed by motion platform stepping
The swept-focus region of formula, time-consuming；Slit rule needs to shoot the image that slit is mutually perpendicular to both direction respectively, and needs
Ensure slit exact vertical twice.Measurement of the above all to gamma-rays pipe focal spot size in practical application in industry brings limit
System.
Gamma-rays pipe focal spot size will significantly affect the spatial resolution of radiation imaging system, while focal spot size can also be made
To weigh the important evidence of ray tube service behaviour.The method of existing measurement gamma-rays pipe focal spot size mainly has scanning method, pin
Kong Fa, Narrow slit and boundary method, these methods have the characteristics of respective, but equal Shortcomings, are required to the specific survey of special preparation
Trial work has, and has stricter limitation to test condition.
Prior art discloses a kind of ray detector of nuclear medical imaging device, including scintillation crystal, condenser lens and
Optical-electrical converter, its main points are that cross sectional shape of the cross section with scintillation crystal of condenser lens, size are identical, and optical-electrical converter is set
Put in focal beam spot minimum, light intensity maximum.Both the utilization rate to exporting optical signal had been greatly improved, opto-electronic conversion can be reduced again
The size of device, greatly reduce the dark current of optical-electrical converter, but improve optical-electrical converter combination property and resolution ratio compared with
It is low.
At present, non-crystalline silicon ray detector：The nucleus module of Medical Devices is mainly used in, is to receive ray to produce telecommunications
Number, and the component for image is handled, it includes scintillation crystal layer, photodiode layer and TFT backplate layer, wherein scintillation crystal layer
Ray can be converted into visible ray, photodiode can convert optical signals to electric signal, and TFT backplate can read out electric signal
Come.
In the structure of detector, photoelectric diode is a crucial part, and the conversion efficiency of photodiode determines
Many performances such as signal to noise ratio, resolution.
In summary, the problem of prior art is present be：The photodiode layer of existing detector sink to the bottom be it is complete flat,
There is no a light trapping effect, photoelectric transformation efficiency is relatively low；Diode material lacking toughness；Moreover, the carrier mobility of diode is not
Enough height, the sensitivity of the ray detector so formed is not high enough, often leads to the radiographic source for needing intensity very high so that make
It is higher with the cost of ray detector；And focal spot size measurement degree is not high in the prior art.
The content of the invention
To solve the problems, such as that prior art is present, the utility model provides a kind of penetrating for nuclear medical imaging device SPECT/CT
Line detector.
The utility model is adopted the technical scheme that to solve technical problem present in known technology：A kind of nuclear medicine
Imaging device SPECT/CT ray detector, it is provided with gamma-rays pipe；Multiple cone-beam lead holes are provided with the gamma-rays pipe；Institute
State and be inlaid with photodiode inside gamma-rays pipe；The emergent light end of the photodiode is contained in cone-beam lead hole；It is described
The lower end in cone-beam lead hole is spaced for will incide ray and be converted to the ray conversion layer of visible ray；
The ray conversion layer lower end, which is equipped with, to be etched into the photodiode glass with globoidal structure and sinks to the bottom layer；
The photodiode glass with globoidal structure sinks to the bottom a layer lower end and is equipped with it will be seen that light is converted to electric charge letter
Number photoelectric conversion layer；
The photoelectric conversion layer lower end is equipped with the pel array with multiple pixels for detecting the charge signal
Layer；
The pel array layer lower end is equipped with layer of lead glass；
It is separated between the layer of lead glass lower end and reads data circuit flaggy.
Further, each pixel in the pel array layer includes pixel switch, pixel electrode and public electrode；It is described
Pixel electrode electrically connects with the source electrode of the pixel switch or drain electrode；The public electrode and the pixel electrode and the photoelectricity
Conversion layer contacts.
Further, the photodiode glass with globoidal structure, which is sunk to the bottom, is attached with wavelength turn on the globoidal structure of layer
Change coating；The epitaxial wafer surface etch of photodiode has circular arc graphic structure.
Further, the circular arc graphic structure of the epitaxial wafer surface etch of photodiode or be isolated groove.
Further, the globoidal structure is concave structure.
The utility model has the advantages and positive effects of：The sensitivity of the utility model ray detector is very high, energy
External signal processing system is enough allowed more easily to detect charge signal, so as to carry out ray with the relatively low radiographic source of energy
Detection；So that the use cost of ray detector is relatively low, and be advantageous to save the energy.
The utility model is provided with globoidal structure, solve existing detector photodiode sink to the bottom be it is complete flat,
There is no light trapping effect, the relatively low technical problem of photoelectric transformation efficiency.
The light of photodiode transmitting of the present utility model is by reflecting, reflecting and scatter；Incident ray is distributed to respectively
Individual angle, the light that the photodiode glass with globoidal structure etched so as to increase light on crystal Rotating fields sinks to the bottom layer are inhaled
Yield.
The circular arc graphic structure of photodiode etching of the present utility model solves photodiode for isolated groove
Very thick mask layer need not be grown, circular arc graphic structure is reduced or isolated groove forms the time, reduce process length, carry
The high yield of product, greatly reduces product cost.And worked using Non-scanning mode mode, time of measuring is extremely short, and speed is fast,
The real-time detection of gamma-rays diffracting spectrum is realized, especially suitable for in-situ study and on-line analysis.
The wavelength convert coating adhered in the utility model cambered surface be aluminum tungstate, bismuth germanium oxide, barium fluoride, in silicic acid lutetium extremely
Few one kind, the particle of above-mentioned coating is tiny, and the specific wavelength visible ray that multiple particles are sent can be ensure that specific with simultaneous transmission
The reception conduction efficiency of visible light wavelengths, and improve the signal to noise ratio of later stage signal transacting.Can be by material with thin layer during production
Form is coated on the outside of concave surface, forms conversion coating.
The conversion coating that gamma-rays after diffraction is diffracted on line concave surface receives and changed the visible ray for being changed into specific wavelength,
The visible ray of specific wavelength enters through pel array layer and conducted to data circuit flaggy is read, and most optical signal changes in real time at last
For data signal, gamma-ray real-time diffracting spectrum is obtained.It is of the present utility model detection the measuring speed fast single measurement time be
Millisecond.The utility model, which does not have to below external circuit add again, covers stereotype, so as to add the mechanical strength of product, reduces
Due to damage of the covering stereotype to external circuit, the yield rate of product is improved.
Brief description of the drawings
Fig. 1 is the ray detector schematic diagram for the nuclear medical imaging device SPECT/CT that the utility model embodiment provides；
Fig. 2 is the photodiode schematic diagram that the utility model embodiment provides.
Fig. 3 is the wavelength convert coating schematic diagram that the utility model embodiment provides.
In figure：1st, gamma-rays pipe；2nd, cone-beam lead hole；3rd, photodiode；3-1, circular arc graphic structure；4th, ray is changed
Layer；5th, the photodiode glass with globoidal structure sinks to the bottom layer；6th, photoelectric conversion layer；7th, pel array layer；8th, layer of lead glass；
9th, data circuit flaggy is read；10th, wavelength convert coating.
Embodiment
For invention, features and effects of the present utility model can be further appreciated that, following examples are hereby enumerated, and coordinate
Accompanying drawing describes in detail as follows.
Structure of the present utility model is explained in detail below in conjunction with the accompanying drawings.
As shown in Figure 1 to Figure 3, the X-ray detection X for the nuclear medical imaging device SPECT/CT that the utility model embodiment provides
Device, it is provided with gamma-rays pipe 1；Multiple cone-beam lead holes 2 are provided with the gamma-rays pipe 1；Light is inlaid with inside the gamma-rays pipe
Electric diode 3；The emergent light end of the photodiode 3 is contained in cone-beam lead hole；The lower end interval row in the cone-beam lead hole
Show for ray will be incided to be converted to the ray conversion layer 4 of visible ray；
The lower end of ray conversion layer 4, which is equipped with, to be etched into the photodiode glass with globoidal structure and sinks to the bottom layer 5；
The photodiode glass with globoidal structure sinks to the bottom the lower end of layer 5 and is equipped with it will be seen that light is converted to electric charge letter
Number photoelectric conversion layer 6；
The lower end of photoelectric conversion layer 6 is equipped with the pel array with multiple pixels for detecting the charge signal
Layer 7；
The lower end of pel array layer 7 is equipped with layer of lead glass 8；
It is separated between the lower end of layer of lead glass 8 and reads data circuit flaggy 9.
Each pixel in the pel array layer 8 includes pixel switch, pixel electrode and public electrode；The pixel electricity
Pole electrically connects with the source electrode of the pixel switch or drain electrode；The public electrode and the pixel electrode and the photoelectric conversion layer
Contact.
The photodiode glass with globoidal structure, which is sunk to the bottom, is attached with wavelength convert coating on the globoidal structure of layer 5
10；The epitaxial wafer surface etch of photodiode 3 has circular arc graphic structure 3-1.
The circular arc graphic structure of the epitaxial wafer surface etch of photodiode 1 is isolated groove.
The globoidal structure is concave structure.
The sensitivity of the utility model ray detector is very high, and external signal processing system can be allowed more easily to detect
Charge signal, so as to carry out X-ray detection X with the relatively low radiographic source of energy；So that the use cost of ray detector is relatively low,
And be advantageous to save the energy.
The utility model is provided with globoidal structure, solve existing detector photodiode sink to the bottom be it is complete flat,
There is no light trapping effect, the relatively low technical problem of photoelectric transformation efficiency.
The light of photodiode transmitting of the present utility model is by reflecting, reflecting and scatter；Incident ray is distributed to respectively
Individual angle, the light that the photodiode glass with globoidal structure etched so as to increase light on crystal Rotating fields sinks to the bottom layer are inhaled
Yield.
The circular arc graphic structure of photodiode etching of the present utility model solves photodiode for isolated groove
Very thick mask layer need not be grown, circular arc graphic structure is reduced or isolated groove forms the time, reduce process length, carry
The high yield of product, greatly reduces product cost.And worked using Non-scanning mode mode, time of measuring is extremely short, and speed is fast,
The real-time detection of gamma-rays diffracting spectrum is realized, especially suitable for in-situ study and on-line analysis.
The wavelength convert coating adhered in the utility model cambered surface be aluminum tungstate, bismuth germanium oxide, barium fluoride, in silicic acid lutetium extremely
Few one kind, the particle of above-mentioned coating is tiny, and the specific wavelength visible ray that multiple particles are sent can be ensure that specific with simultaneous transmission
The reception conduction efficiency of visible light wavelengths, and improve the signal to noise ratio of later stage signal transacting.Can be by material with thin layer during production
Form is coated on the outside of concave surface, forms conversion coating.
The conversion coating that gamma-rays after diffraction is diffracted on line concave surface receives and changed the visible ray for being changed into specific wavelength,
The visible ray of specific wavelength enters through pel array layer and conducted to data circuit flaggy is read, and most optical signal changes in real time at last
For data signal, gamma-ray real-time diffracting spectrum is obtained.It is of the present utility model detection the measuring speed fast single measurement time be
Millisecond.The utility model, which does not have to below external circuit add again, covers stereotype, so as to add the mechanical strength of product, reduces
Due to damage of the covering stereotype to external circuit, the yield rate of product is improved.Improve the acceptance rate of diffracting spectrum.
Further described with reference to specific embodiment operation principle of the present utility model.
The R ray tubes used are single anode cermet gamma-rays pipe；Target material is tungsten, and target angle α is 20 °, largest tube electricity
Press as 225kV, lead taper hole thickness l2=14.0mm；Detector is amorphous silicon detector, and saturation count rate is 50910；Geometry position
It is l to put parameter1=37.0mm, l3=131.0mm, β=16 °, s=0.127mm.
1st, it is using focal spot size measuring method of the present utility model：
Using the cone-beam lead hole on gamma-rays pipe, the light field being emitted using detector shooting ray from cone-beam lead hole；
Reading data circuit flaggy, why not acutance calculates focal spot size using light field edge several.
2. experiment
2.1 experimental method
The area of the beam bombardment of gamma-rays tube cathode transmitting to anode target surface is referred to as " actual focal spot ", and in gamma-rays
Pipe in use, what is be generally concerned with is the projection of " actual focal spot " in gamma-rays exit direction, i.e. " effective focal spot ", its size
Relevant with the target angle of gamma-rays pipe, the focal spot size provided is " effective focal spot ".
Gamma-rays pipe focal spot size is represented by the length of transverse direction (x) and longitudinal direction (y) both direction, is respectively defined as long L
It is transverse center section with wide W) and longitudinal center section, it respectively obtains the L of focal spot size and W.
Target angle is α, off-target dot center distance l1It is l that, which there is thickness at place,2Lead taper hole, subtended angle is 2 β, and β is less than or equal to α.
Target surface is perpendicular to center gamma-rays exit direction (- z).
If focus is a preferable point, then it radiates subtended angle will exactly 2 β, but actual conditions are that focus is present
Certain size, it will be modulated from the gamma-rays of focal point transmitting by lead taper hole, the γ for showing as the transmitting of focus side is penetrated
Line will be prevented by lead taper hole upper edge and can only reach the region smaller than β angle, and the gamma-rays of focus opposite side transmitting can be from cone
Lead hole lower edge reaches the region bigger than β angle, this phenomenon is referred to as " broadening effect ", this can cause the edge mould of light field
Paste, fuzzy scope (a1a3) it is referred to as " why not several acutance ".
In transverse plane, because target surface and center gamma-rays exit direction (- z directions) have angle α, cause on the right side of light field
Several why not acutance is much larger than left side, and vertical with center Γ ray exit directions in fore-and-aft plane, target surface, therefore light field is upper and lower
Both sides are symmetrical.
From lead taper hole distance l3Detector is placed perpendicular to z-axis and ensures that detector covers the whole light field of Γ ray tubes in place
Region, using detector shoot gamma-rays pipe optical field distribution, obtain light field edge it is several why not acutance a1a3, in conjunction with focus,
Focal spot size can be calculated in the geometrical relationship of lead taper hole and detector.The definition of coordinate direction is such as gamma-rays pipe focal spot size
Represented by the length of horizontal and vertical both direction, be respectively defined as long L and wide W.
By shooting gamma-rays pipe light field, light field central point a can be found in detector output image data0Pixel position
Put, and point a is found at light field edge1、a2、a3Location of pixels, l1、l2, it is known that l3It can simply measure to obtain, then γ direction of principal axis is burnt
The length L of point can be obtained by (1) formula：
L=c1L1+c2L2 (1)
Wherein L1、L2Represent line segment, c1、c2L is represented respectively1、L2Tribute to center Γ rays exit direction " effective focal spot "
Offer coefficient；L1、L2According to the geometrical relationship of similar triangles, can be obtained by (2) formula：
Projection coefficient c1、c2It can be obtained by (3) formula：
tan(θ1)、tan(θ3) obtained by (4) formula：
Wherein, s is detector pixel width, and α is target angle, l1、l2And l3Respectively focus center to lead taper hole upper surface away from
From, lead taper hole thickness and lead taper hole lower surface to detector distance, θ1And θ3Respectively ray is in a1And a3Place and the folder of detector
Angle.
On y-axis direction, target surface is vertical with z-axis, projection coefficient 1, and the width W of focus is obtained by (5) formula：
W=W1+W2 (5)
Wherein W1、W2Obtained by (6) formula：
The method that focal spot size accurately calculates is presented above, under approximate condition, the L and W of focal spot size respectively can be by
(7) obtained with (8) formula approximation, in l2Relative to l1When smaller, i.e., when lead taper hole is relatively thin, the approximate calculation method can obtain and essence
Result similar in true computational methods.
2.2 experiment condition
The gamma-rays pipe that this experiment uses is industrially to widely use single anode cermet gamma-rays pipe, its target material
For tungsten, target angle α is 20 °, and maximum tube voltage is 225kV, lead taper hole thickness l2=14.0mm.Flat panel detector is amorphous silicon flat panel
Detector, wherein number of pixels are 1024 × 1024, and Pixel Dimensions are 0.127mm × 0.127mm, and saturation count rate is 50910.
Other geometric position parameters are l1=37.0mm, l3=131.0mm, β=16 °, s=0.127mm.
3. result is with discussing
3.1 gamma-rays pipe light fields
The light field of gamma-rays pipe is directly shot using detector, wherein Γ ray tubes tube voltage is 169kV, and tube current is
0.1mA, flat panel detector frame per second are 30 width/s, are continuously shot 150 width light field images, and take its average value to be used as and be used to calculate Jiao
The light field image of spot size, to reduce the error that statistic fluctuation is brought.The light field of gamma-rays pipe is mainly imitated by anode effect, broadening
Should and target angle influence, anode effect causes light field generally nearly cathode terminal transmitted intensity high and nearly anode tap transmitted intensity is low,
Broadening effect then causes light field blurred edges and light field region becomes big, and target angle can cause light field both lateral sides edge asymmetric, closely
Cathode terminal edge broadening is obvious and nearly anode tap edge broadening is very narrow.
The light field of the large and small focus of gamma-rays pipe, the intensity distribution deviation cathode terminal (on the right side of x-axis direction) of light field, and vertical
It is then symmetrical to upper and lower both sides light field.In addition, light field edge obscures, and why not acutance is significantly greater than by large focal spot several
Small focus.Gamma intensity curve can be drawn by taking the center row and column of the large and small focus light field of gamma-rays pipe.
3.2 focal spot size
The derivation of focal spot size measuring method and calculation formula, can be smart respectively by (1)~(4) formula and (5)~(6) formula
Really calculate the long L and wide W of focal spot size.
In x-axis direction, actual equivalent focus can change with the change of observation angle, actual further away from center
Equivalent focus size is bigger, and at light field edge, the maximum for measuring large focal spot length L is 4.02, small Focus length L maximum
For 0.88, slightly larger than reference value of dispatching from the factory；The measurement result of large and small focus shows consistent trend；
In addition, being separated by the experiment of one week twice has obtained almost identical result, show that experiment has preferably repeatability
And operability.
The influence of 3.3 tube voltages focusing spot size
The focus measuring method of proposition has further probed into the tube voltage focusing spot size of industrial conventional gamma-rays pipe
Influence, select tube voltage to measure the focal spot size of gamma-rays pipe for 75kV, 100kV and 169kV respectively.
This focus measuring method is applied to COMET companies MRR225/22 type gamma-rays pipes, and measurement result accurately reflects
The ratio of large and small focal spot size, the wide W and reference value relative deviation of focal spot size are smaller, long L and the reference value phase of focal spot size
Larger to deviation, L numerical value changes with X direction measurement angle.In addition, result also shows focal spot size not by tube voltage
Influence.
Described above is only to preferred embodiment of the present utility model, not the utility model is made any formal
Limitation, it is every according to the technical essence of the utility model to any simple modification made for any of the above embodiments, equivalent variations with
Modification, is belonged in the range of technical solutions of the utility model.
Claims (5)
- A kind of 1. nuclear medical imaging device SPECT/CT ray detector, it is characterised in that the nuclear medical imaging device SPECT/CT ray detector is provided with gamma-rays pipe；Multiple cone-beam lead holes are provided with the gamma-rays pipe；The gamma-rays Photodiode is inlaid with inside pipe；The emergent light end of the photodiode is contained in cone-beam lead hole；The cone-beam lead hole Lower end be spaced for ray will be incided to be converted to the ray conversion layer of visible ray；The ray conversion layer lower end, which is equipped with, to be etched into the photodiode glass with globoidal structure and sinks to the bottom layer；The photodiode glass with globoidal structure sinks to the bottom a layer lower end and is equipped with it will be seen that light is converted to charge signal Photoelectric conversion layer；The photoelectric conversion layer lower end is equipped with the pel array layer with multiple pixels for detecting the charge signal；The pel array layer lower end is equipped with layer of lead glass；It is separated between the layer of lead glass lower end and reads data circuit flaggy.
- 2. nuclear medical imaging device SPECT/CT as claimed in claim 1 ray detector, it is characterised in that the pixel battle array Each pixel in row layer includes pixel switch, pixel electrode and public electrode；The pixel electrode and the pixel switch Source electrode or drain electrode electrical connection；The public electrode and the pixel electrode contact with the photoelectric conversion layer.
- 3. nuclear medical imaging device SPECT/CT as claimed in claim 1 ray detector, it is characterised in that described that there is arc The photodiode glass of face structure, which is sunk to the bottom, is attached with wavelength convert coating on the globoidal structure of layer；The epitaxial wafer of photodiode Surface etch has circular arc graphic structure.
- 4. nuclear medical imaging device SPECT/CT as claimed in claim 1 ray detector, it is characterised in that photodiode Epitaxial wafer surface etch circular arc graphic structure or be isolated groove.
- 5. nuclear medical imaging device SPECT/CT as claimed in claim 1 ray detector, it is characterised in that the cambered surface knot Structure is concave structure.
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| CN201720443746.9U CN206671574U (en) | 2017-04-17 | 2017-04-17 | A kind of nuclear medical imaging device SPECT/CT ray detector |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2020143486A1 (en) * | 2019-01-11 | 2020-07-16 | 惠科股份有限公司 | Ray converter and ray detection panel device |
| CN113376682A (en) * | 2021-06-30 | 2021-09-10 | 散裂中子源科学中心 | Method and system for measuring high-energy proton beam spot in front of target |
| CN114289876A (en) * | 2021-12-30 | 2022-04-08 | 华中科技大学 | Scintillation crystal and processing method thereof, detector and application thereof |
-
2017
- 2017-04-17 CN CN201720443746.9U patent/CN206671574U/en not_active Expired - Fee Related
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2020143486A1 (en) * | 2019-01-11 | 2020-07-16 | 惠科股份有限公司 | Ray converter and ray detection panel device |
| US11561309B2 (en) | 2019-01-11 | 2023-01-24 | HKC Corporation Limited | Ray converter and ray detection panel device |
| CN113376682A (en) * | 2021-06-30 | 2021-09-10 | 散裂中子源科学中心 | Method and system for measuring high-energy proton beam spot in front of target |
| CN114289876A (en) * | 2021-12-30 | 2022-04-08 | 华中科技大学 | Scintillation crystal and processing method thereof, detector and application thereof |
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