CN109893155A - A kind of notch method for manufacturing collimator for gamma camera - Google Patents
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- CN109893155A CN109893155A CN201910164237.6A CN201910164237A CN109893155A CN 109893155 A CN109893155 A CN 109893155A CN 201910164237 A CN201910164237 A CN 201910164237A CN 109893155 A CN109893155 A CN 109893155A
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- 238000000034 method Methods 0.000 title claims abstract description 34
- 238000004519 manufacturing process Methods 0.000 title claims abstract description 16
- 238000013461 design Methods 0.000 claims abstract description 24
- 238000003384 imaging method Methods 0.000 claims abstract description 20
- 210000004072 lung Anatomy 0.000 claims abstract description 20
- 230000005855 radiation Effects 0.000 claims description 11
- 210000000115 thoracic cavity Anatomy 0.000 claims description 6
- WFKWXMTUELFFGS-UHFFFAOYSA-N tungsten Chemical compound [W] WFKWXMTUELFFGS-UHFFFAOYSA-N 0.000 claims description 6
- 229910052721 tungsten Inorganic materials 0.000 claims description 6
- 239000010937 tungsten Substances 0.000 claims description 6
- 239000000463 material Substances 0.000 claims description 4
- 230000003321 amplification Effects 0.000 claims description 3
- 238000003199 nucleic acid amplification method Methods 0.000 claims description 3
- 239000000126 substance Substances 0.000 claims description 3
- 230000000694 effects Effects 0.000 abstract description 9
- 210000000056 organ Anatomy 0.000 abstract description 6
- 238000001514 detection method Methods 0.000 description 7
- 238000003491 array Methods 0.000 description 5
- 238000009206 nuclear medicine Methods 0.000 description 4
- 238000010586 diagram Methods 0.000 description 3
- 238000012986 modification Methods 0.000 description 3
- 230000004048 modification Effects 0.000 description 3
- 210000001541 thymus gland Anatomy 0.000 description 3
- 210000001519 tissue Anatomy 0.000 description 3
- 238000002474 experimental method Methods 0.000 description 2
- 230000005251 gamma ray Effects 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 238000012545 processing Methods 0.000 description 2
- 230000000007 visual effect Effects 0.000 description 2
- 238000010146 3D printing Methods 0.000 description 1
- 241000208340 Araliaceae Species 0.000 description 1
- 235000005035 Panax pseudoginseng ssp. pseudoginseng Nutrition 0.000 description 1
- 235000003140 Panax quinquefolius Nutrition 0.000 description 1
- 238000004364 calculation method Methods 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 238000013016 damping Methods 0.000 description 1
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- 230000008021 deposition Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 230000002708 enhancing effect Effects 0.000 description 1
- 235000008434 ginseng Nutrition 0.000 description 1
- 238000003754 machining Methods 0.000 description 1
- 239000011159 matrix material Substances 0.000 description 1
- 238000005555 metalworking Methods 0.000 description 1
- 238000012544 monitoring process Methods 0.000 description 1
- 230000003287 optical effect Effects 0.000 description 1
- 230000000737 periodic effect Effects 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 230000002685 pulmonary effect Effects 0.000 description 1
- 238000002601 radiography Methods 0.000 description 1
- 210000002345 respiratory system Anatomy 0.000 description 1
- 239000007787 solid Substances 0.000 description 1
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Abstract
The invention discloses a kind of notch method for manufacturing collimator for gamma camera comprising the encoding array design method, notch resolution ratio design method and encoding board Thickness Design Method of encoding board on promising collimation device；This programme so that encoding board becomes collimator, and is designed by opening up square hole according to certain mathematical law on encoding board according to human lung's size, good to high-energy ray shield effectiveness, is played a key effect to imaging organs' effect, highly reliable.
Description
Technical field
The present invention relates to the technical fields of gamma radiation imaging, and in particular to a kind of notch collimation for gamma camera
Device production method.
Background technique
Compared to traditional core activity-sensing equipment, the capacity superiority that gamma camera differentiates nucleic position is obvious, matches
Optical imagery is closed, directly nucleic can be positioned.Currently used gamma camera system is by detector system and collimator
System composition, wherein colimated light system can form the certain shapes profile radiation visual field, stop the primary radiation outside absolute visual field, pass through
Aperture changes the propagation trajectories of photon, can achieve enhancing System spatial resolution, the effect for increasing image-forming range.By right
Different types of collimator allows gamma camera to be used in different nuclear radiation imaging fields.Used in nuclear radiation field
Collimator is many kinds of, such as pinhole collimator, Fresnel wave plate collimator, random array collimator, notch collimator etc..
1961, Mert.L and Yong proposed coded aperture imaging technique, will by the raising of detection efficient by the aperture of notch
The difficulty of imaging technique is converted into the calculation amount of computer, while meeting the requirement of imaging precision and imaging time.1971
The shortcomings that L.J.Meng and D.K.Wehe proposes non-redundant arrays (Non-Redundant Arrays, NRA), non-redundant arrays master
Will there are two: first is that, second is that small hole number is very little, causing the radiography acquisition efficiency of system too low without ideal imaging characteristic.
Nevertheless, non-redundant arrays are still largely used in nuclear medicine studies field.Gottesmen was in the base in URA in 1989
It is proposed on plinth and corrects uniform redundancy (Modified Uniformly Redundant Arrays, MURA) array, i.e. MURA gusts
Column.It possesses all advantages of URA, and rectangular construction is so that the design and processing of encoding board are more convenient.Different standards
Straight device can apply to different Radiation monitoring fields, such as the pinhole collimator and parallel aperture collimator of nuclear medicine, use
It is spatial discrimination height, small volume in the characteristics of collimator of nuclear medicine.The design principle of pinhole collimator leads to its detection
Efficiency it is low, be only used for the measurement of the high activity nucleic of low energy in nuclear medicine.
In nuclear accident, nucleic enters lung by respiratory tract and forms interior irradiation, the nucleic release of pulmonary deposition
Gamma rays energy range is wide, and nuclide energy is high, and the collimator for causing current gamma camera to use cannot be to multiple kinds of energy nucleic
It is imaged.It needs that high-energy gamma rays is imaged in pollution condition in lung, simultaneously because the low requirement of lung's nucleic activity
Near-Field Radar Imaging is to obtain better spatial resolution and detection efficient.
It therefore in view of this, can be under nuclear accident to the standard that pollution is imaged in lung for how to search out one kind
Straight device system is just particularly important.
Summary of the invention
In view of the deficiencies in the prior art, the purpose of the present invention is to provide a kind of notches for gamma camera
Human Lung inside high-energy gamma rays can be imaged in method for manufacturing collimator, the notch method for manufacturing collimator,
Have good spatial resolution and detection efficient.
To achieve the above object, The technical solution adopted by the invention is as follows:
A kind of notch method for manufacturing collimator for gamma camera, the production method of the notch collimator include
The encoding array design method, notch resolution ratio design method and encoding board thickness design of encoding board on promising collimation device
Method；
The encoding array design method are as follows: be based on MURA pattern array Bp×qIn any one element Bij, wherein p=q,
And p, q are prime number；
Wherein number 1 indicates not aperture, 0 mark aperture；
The design method of the notch resolution ratio are as follows: notch resolution lambda are as follows:
Wherein pmFor the side length of the notch on encoding board, m is the amplification factor of system, and b is the object distance in imaging system,
A is the focal length in imaging system；
The encoding board Thickness Design Method are as follows: coding plate thickness L are as follows:
Wherein I0For the starting exposure rate of ray, I is to pass through the radiation exposure dose rate after substance, μ1For corresponding photon pair
Line attenuation coefficient in medium.
Further, the encoding board is to be made using tungsten material.
Further, the size dimension d of the notch collimatormFor lung's thoracic cavity width in radiation artificial human body model
Twice.
Further, resolution lambda=p of the notchm, wherein m=1.
Further, the thickness L of the encoding board is 1.93cm.
Compared with prior art, the advantageous effects that this programme has are as follows: this programme by encoding board according to one
Fixed mathematical law opens up square hole, so that encoding board becomes collimator, and is designed according to human lung's size,
It is good to high-energy ray shield effectiveness, it plays a key effect to imaging organs' effect, it is highly reliable.
Detailed description of the invention
Fig. 1 is simulated humanbody thoracic cavity model schematic in the present invention.
Fig. 2 is the collimator schematic diagram in the present invention after nestingization.
Fig. 3 is system geometric resolution schematic diagram in the present invention.
In figure:
The right lung tissue of 1-, the left lung tissue of 2-, 3- heart, 4- thymus gland body, 5- human spine, 6- shoulder blade.
Specific embodiment
The present invention is described in further detail with specific embodiment with reference to the accompanying drawings of the specification.
This programme be multiple kinds of energy nucleic cannot be carried out for collimator used in existing current gamma camera at
Picture, and a kind of notch collimator production side for gamma camera that there is a problem of that detection efficient is low, and then propose
Human Lung inside high-energy gamma rays can be imaged in method, the notch method for manufacturing collimator, have good sky
Between resolution ratio and detection efficient.
This programme is in order to solve the problems, such as under nuclear accident the near field joint imaging for polluting multicore element in lung, and the one of proposition
Kind can be specific as follows for the production method of the uniform redundant array (code aperture collimator) for the imaging polluted in lung:
1, the code Design method of notch collimator:
In all coded imaging modes, MURA coding mode is in auto-correlation coefficient, symmetry, percent opening, machining
Aspect of performance suffers from preferable performance.In the design of MURA, MURA can be understood as a kind of special pattern of URA, even if
Ranks number is equal.It is assumed that B in MURA modep×q, then p=q, and p, q are prime number.Any one element in MURA array
Bij, definition can be defined according to URA definition mode coding mode.
In formula 1:
It is calculated according to above-mentioned formula 1, both whether the aperture of each element of available MURA, wherein 1 indicates not open
Hole, 0 indicates aperture.
In radiation emulation experiment, radiation artificial human body model is a kind of stylized body mould of mathematics, the stylized body mould of mathematics
It is to simplify each human organ, indicates human organ by a series of fundamental figures and combination.The geometry of human organ
Mathematical formulae can be used to be described in size, and each organ is finally grouped together into manikin.In conjunction with
It is simulated humanbody thoracic cavity illustraton of model referring to shown in attached drawing 1.It includes human body or so lung tissue 1,2, human heart 3, thymus gland
Body 4, human spine 5 and shoulder blade 6, lung model are half of spheroid, and volume is a 11cm × 16cm × 24cm, density
For 0.2958g/cm3；The density of human heart 3 is 0.9869g/cm3；The density of thymus gland body 4 is 0.9869g/cm3；Middle section
For human spine 5, density 1.9362g/cm3；The density of shoulder blade 6 is 1.9362g/cm3。
Human lung thoracic cavity width in the present embodiment is about 30cm, and notch collimator design size should compare human body
Thoracic cavity is big, can just obtain whole projection, is twice of size of lung or so, i.e. the size d of notch collimator by collimator sizem
=60cm.In view of current slow wire feeding metal working process and 3D printing technique, by the aperture size P of notchmIt is set as
1cm, therefore the matrix line number and columns 2N=D of MURA coding versionm/pm, according to prime number principle, therefore, N is taken under normal circumstances
Value amplifies value on the original basis, however interior pollution gamma-rays imaging subnumber is relatively fewer, for etendue and
The detection efficient of system, the value of N is smaller than calculated value herein, takes 31.Using nested technological design encoding board, therefore collimate
Device designing unit is set as 31 × 2-1=61, and basic unit is MURA (31 × 31), is MURA (61 × 61) after nested.?
Before collimation device carries out nesting, needs to carry out centralization processing to unit collimator, form centrosymmetric encoding array.It compiles
The centralization of code plate just refers to from 0 row 0 of encoding array B column and does periodic transformation, until the element B of array center positioni,j, from
From the point of view of effect, really with 0 row and 0 column for symmetry axis, B0,0For symmetrical centre, Lai Jinhang centralization.
It is MURA (61 × 61) collimator after nestingization referring to shown in attached drawing 2.Wherein solid position represents not open in figure
Hole, element 1；Blank position represents aperture, element 0.The size of final collimator is dm=61cm.
2, the resolution ratio design of notch:
There are many definition for collimator geometric resolution, generally use the definition method of point spread function full width at half maximum, are
(Full Width at Half-Maximum, FWHM): the distance for being two ideal point sources is D, and image restores latter two point
The centre distance in source is the full width at half maximum of system point spread function, it is believed that point is just separated, and D is that the geometry of system is differentiated at this time
Rate.
The side length in square numbering hole is Pm, then amplified image side length is m × Pm, m is the amplification factor of system；It compiles
It is consistent with the single pin-hole collimator of same size that collimator geometric resolution is imaged in code holes.Therefore, in this experiment MURA (61 ×
61) geometric resolution can be by asking the identical single hole collimator geometric resolution with notch size (1cm) to obtain.In conjunction with ginseng
It is the imaging model schematic diagram of single pin-hole collimator according to shown in attached drawing 3.
It is MURA fundamental length that wherein AB length, which is size,；Distance is λ between two point sources P1, P2, and point P1's is projected as
DE, P2's is projected as CD, and the projection of the two point sources is just separated.The distance between this time point is exactly the geometry difference of encoding board
Rate.By geometrical relationship in Fig. 3, available following formula
Wherein, since measurement environment is the imaging of nearly lung, m=1.Radiation image-forming system can be learnt by formula (2)
Resolution ratio is determined by magnifying power and encoding board nested cell size, unrelated with object distance b and focal length a.The geometry of this collimator is differentiated
Rate Pm=1cm.
3, collimator thickness design:
One beam intensity is I0Monoenergetic gamma rays vertical irradiation to the absorbing medium with a thickness of L on when, gamma ray intensity
It will decay with the increase of incident depth, law of force is according to exponential damping:
I0For the starting exposure rate of ray, I is to pass through the radiation exposure dose rate after substance, μ1It is corresponding photon to medium
In line attenuation coefficient, L be absorbing medium thickness.The shape of collimator is fixed and not for lung's pollution collimator
It can arbitrarily change, tungsten is better than lead for the linear attenuation characteristic of high energy gamma rays, therefore the material of collimator should use
Tungsten W, atomic number 74, density 19.35g/cm3。
The effective cross-section of absorbing medium is as shown in Equation 4:
Above formula is substituted into exposure rate decay formula, obtains 5 formulas:
Coding plate thickness mainly influences entire imaging system to gamma-ray shield effectiveness.This system design coding plate material
Attenuation multiple to the 662keV energy-ray of 137Cs is 20 times, is that energetic gamma rays 5% can pass through encoding board.Cause
This I=0.05 × I0, wherein the density of tungsten is ρ=19.35g/cm3, table look-up to obtain tungsten to the mass attentuation coefficient of 662keV energy
For 0.08/cm, data are substituted into:
0.05×I0=I0×e-0.08×19.35×L (6)
The thickness L=1.93cm of this system MURA encoding board collimator.
Obviously, various changes and modifications can be made to the invention without departing from essence of the invention by those skilled in the art
Mind and range.In this way, if these modifications and changes of the present invention belongs to the range of the claims in the present invention and its equivalent technology
Within, then the present invention is also intended to include these modifications and variations.
Claims (5)
1. a kind of notch method for manufacturing collimator for gamma camera, it is characterised in that: the system of the notch collimator
It include the encoding array design method, notch resolution ratio design method and coding of encoding board on promising collimation device as method
Plate thickness design method；
The encoding array design method are as follows: be based on MURA pattern array Bp×qIn any one element Bij, wherein p=q, and p, q
It is all prime number；
Wherein number 1 indicates not aperture, 0 mark aperture；
The design method of the notch resolution ratio are as follows: notch resolution lambda are as follows:
Wherein pmFor the side length of the notch on encoding board, m is the amplification factor of system, and b is the object distance in imaging system, a be at
As the focal length in system；
The encoding board Thickness Design Method are as follows: coding plate thickness L are as follows:
Wherein I0For the starting exposure rate of ray, I is to pass through the radiation exposure dose rate after substance, μ1It is corresponding photon to medium
In line attenuation coefficient.
2. a kind of notch method for manufacturing collimator for gamma camera according to claim 1, it is characterised in that: institute
Stating encoding board is to be made using tungsten material.
3. a kind of notch method for manufacturing collimator for gamma camera according to claim 1 or 2, feature exist
In: the size dimension d of the notch collimatormIt is twice of lung's thoracic cavity width in radiation artificial human body model.
4. a kind of notch method for manufacturing collimator for gamma camera according to claim 1 or 2, feature exist
In: resolution lambda=p of the notchm, wherein m=1.
5. a kind of notch method for manufacturing collimator for gamma camera according to claim 2, it is characterised in that: institute
The thickness L for stating encoding board is 1.93cm.
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112415741A (en) * | 2020-10-30 | 2021-02-26 | 北方夜视技术股份有限公司 | Glass-made coded aperture collimator and preparation method thereof |
| CN113219510A (en) * | 2021-05-07 | 2021-08-06 | 苏州德锐特成像技术有限公司 | Nuclear radiation imaging collimator micropore positioning method and nuclear radiation imaging device |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112415741A (en) * | 2020-10-30 | 2021-02-26 | 北方夜视技术股份有限公司 | Glass-made coded aperture collimator and preparation method thereof |
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| CN113219510A (en) * | 2021-05-07 | 2021-08-06 | 苏州德锐特成像技术有限公司 | Nuclear radiation imaging collimator micropore positioning method and nuclear radiation imaging device |
| CN113219510B (en) * | 2021-05-07 | 2024-05-31 | 苏州德锐特成像技术有限公司 | Nuclear radiation imaging collimator micropore positioning method and nuclear radiation imaging device |
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