CN109524284A - A kind of radiotherapy x-ray source and x-ray source device - Google Patents
A kind of radiotherapy x-ray source and x-ray source device Download PDFInfo
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- CN109524284A CN109524284A CN201811437049.8A CN201811437049A CN109524284A CN 109524284 A CN109524284 A CN 109524284A CN 201811437049 A CN201811437049 A CN 201811437049A CN 109524284 A CN109524284 A CN 109524284A
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/02—Details
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/02—Details
- H01J35/04—Electrodes ; Mutual position thereof; Constructional adaptations therefor
- H01J35/06—Cathodes
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/02—Details
- H01J35/14—Arrangements for concentrating, focusing, or directing the cathode ray
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Abstract
The present invention discloses a kind of radiotherapy x-ray source and x-ray source device, is related to radiation therapy technology field.Radiotherapy x-ray source includes: substrate；Cold cathode electron emission source is arranged in substrate；Anode transmission target is arranged with cold cathode electron emission source face, can apply electric field between anode transmission target and substrate；Anode transmission target is arranged in backwards to the side of cold cathode electron emission source in filter；Substrate, cold cathode electron emission source, anode transmission target and filter are encapsulated in vacuum cavity.X-ray source device further includes condenser lens and beam-defining clipper using above-mentioned radiotherapy x-ray source.Radiotherapy x-ray source proposed by the present invention, compared with prior art, electronics escapes through cold cathode field emission, does not need to preheat cathode material, low in energy consumption, and for cathode material using face battle array arrangement, launching electronics are high-efficient；X-ray source device, it is small in size using transmission target, it is high-efficient to generate X-ray.
Description
Technical field
The present invention relates to radiation therapy technology field more particularly to a kind of radiotherapy x-ray sources and x-ray source device.
Background technique
Radiotherapy is a kind of local therapeutic approaches using radiation cure tumour, including with X-ray, gamma-rays, grain
Tumour cell or pathological tissues are killed in the radiation of the different forms such as beamlet.It is wherein treated using X-ray as radioactive source, according to X
X-ray machine X tube voltage size is divided into contact treatment (10-60kV), superficial therapy (80-120kV), depth therapy (150-400kV),
X-ray contact treatment is suitable for the surface layers pathological tissues such as cutaneum carcinoma, scar reparation.Existing X-ray radiotherapy unit uses
Hot cathode escapes cathode electronics, runaway electron beam is in anode high voltage as emission source by heating cathode filament to 1000 DEG C
X-ray needed for the lower bombardment anode target of effect generates radiotherapy by bremstrahlen.X-ray source device in the prior art is extremely
It is few that there are the following problems:
(1) using hot cathode as electron emission source, the operating temperature of hot cathode is high, and power consumption is big；
(2) radiation source device volume is larger, is not easy to realize miniaturization；
(3) the X-ray angle of divergence being emitted is excessive, only carries out limit beam by collimator, causes irradiated area big, just to increase
Normal tissue radiation risk；
(4) anode target uses reflecting target, generates X-ray low efficiency.
Summary of the invention
In view of the above-mentioned problems, it is an object of the invention to propose a kind of radiotherapy x-ray source, with prior art phase
Than low in energy consumption without preheating to cathode material, launching electronics are high-efficient.
Another object of the present invention is to propose a kind of x-ray source device, small in size using transmission target, generates X-ray effect
Rate is high.
The invention adopts the following technical scheme:
A kind of radiotherapy x-ray source, radiotherapy x-ray source include:
Substrate；
Cold cathode electron emission source, setting is on substrate；
Anode transmission target is arranged with cold cathode electron emission source face, can apply electricity between anode transmission target and substrate
?；
Anode transmission target is arranged in backwards to the side of cold cathode electron emission source in filter；
Substrate, cold cathode electron emission source, anode transmission target and filter are encapsulated in vacuum cavity.
As a preferred solution of the present invention, the gap between substrate and anode transmission target is adjustable.Control electron emission
Efficiency, and then control x-ray flux.
As a preferred solution of the present invention, cold cathode electron emission source is multiple, and array is arranged on substrate.
As a preferred solution of the present invention, cold cathode electron emission source is by carbon nanotube or zinc-oxide nano wire material
It is made.
As a preferred solution of the present invention, substrate is made of ITO conducting glass material or metal material.
As a preferred solution of the present invention, anode transmission target and the flaky structure of filter, anode transmission target
It is made of metal material with filter.
As a preferred solution of the present invention, anode transmission target is made of tungsten or metal molybdenum；Filter is by metal
Aluminium or metallic beryllium are made.
As a preferred solution of the present invention, radiotherapy x-ray source further includes power supply module, power supply module respectively with
Substrate and the electrical connection of anode transmission target；Power supply module applies cathode high voltage electricity towards one end of anode transmission target in substrate and connects
Ground, power supply module apply anode high voltage electricity towards one end of substrate in anode transmission target.
As a preferred solution of the present invention, the voltage applied between substrate and anode transmission target is 10kV-60kV.
A kind of x-ray source device, the limit of the exit end including radiotherapy x-ray source and positioned at radiotherapy x-ray source
Beam device, the above-mentioned radiotherapy x-ray source of radiotherapy x-ray source further includes condenser lens, and condenser lens is located at beam-defining clipper backwards
One end of radiotherapy x-ray source.
As a preferred solution of the present invention, the gap between radiotherapy x-ray source and beam-defining clipper is adjustable.
The invention has the benefit that
A kind of radiotherapy x-ray source proposed by the present invention, cold cathode electron emission source are arranged on substrate, and in anode
Apply electric field between transmission target and substrate, so that the electron beam that cold cathode electron emission source is launched, under the action of electric field, electricity
Beamlet bombards anode target, by bremstrahlen, generates X-ray；Anode transmission target is set backwards to the side of cold cathode electron emission source
The filter set can cross the X-ray for absorbing low energy, so that the quality for the X-ray being emitted from radiotherapy x-ray source is more preferably.
Compared with prior art, it does not need to preheat cathode material, radiotherapy x-ray source is low in energy consumption.
A kind of x-ray source device proposed by the present invention, including radiotherapy x-ray source and be located at radiotherapy x-ray source
Exit end beam-defining clipper and the beam-defining clipper other end condenser lens, radiotherapy x-ray source use above-mentioned radiotherapy
X-ray source, so that the X-ray that radiotherapy x-ray source issues, after carrying out limit beam by beam-defining clipper, then by condenser lens penetrates X
Line is focused, and irradiation face size is effectively controlled, reduces x-ray source device when in use to normal group
Radiation risk is knitted, while improving the x-ray flux irradiated in unit area, improves radiotherapy efficiency.
Detailed description of the invention
Fig. 1 is the structural schematic diagram of x-ray source device provided by the invention；
Fig. 2 is the structural schematic diagram of radiotherapy x-ray source provided by the invention.
In figure:
1, beam-defining clipper；2, condenser lens；3, radiotherapy x-ray source；
31, substrate；32, cold cathode electron emission source；33, anode transmission target；34, filter.
Specific embodiment
To keep the technical problems solved, the adopted technical scheme and the technical effect achieved by the invention clearer, below
It will be described in further detail in conjunction with technical solution of the attached drawing to the embodiment of the present invention, it is clear that described embodiment is only
It is a part of the embodiment of the present invention, instead of all the embodiments.Based on the embodiments of the present invention, those skilled in the art exist
Every other embodiment obtained under the premise of creative work is not made, shall fall within the protection scope of the present invention.
In the description of the present invention unless specifically defined or limited otherwise, term " connected ", " connection ", " fixation " are answered
It is interpreted broadly, for example, it may be being fixedly connected, may be a detachable connection, or is integral；It can be mechanical connection,
It can be electrical connection；It can be directly connected, the company inside two elements can also be can be indirectly connected through an intermediary
Logical or two elements interaction relationship.For the ordinary skill in the art, can be understood with concrete condition above-mentioned
The concrete meaning of term in the present invention.
In the present invention unless specifically defined or limited otherwise, fisrt feature second feature "upper" or "lower"
It may include that the first and second features directly contact, also may include that the first and second features are not direct contacts but pass through it
Between other characterisation contact.Moreover, fisrt feature includes the first spy above the second feature " above ", " above " and " above "
Sign is right above second feature and oblique upper, or is merely representative of first feature horizontal height higher than second feature.Fisrt feature exists
Second feature " under ", " lower section " and " following " include that fisrt feature is directly below and diagonally below the second feature, or is merely representative of
First feature horizontal height is less than second feature.
Fig. 1 is the structural schematic diagram of x-ray source device provided by the invention, and Fig. 2 is that radiotherapy X provided by the invention is penetrated
Shown in the structural schematic diagram of line source, complex chart 1 and Fig. 2, which mainly includes coaxial and successively spaced puts
Penetrate treatment x-ray source 3, beam-defining clipper 1 and condenser lens 2.Wherein radiotherapy x-ray source 3 is used for producing X-ray, beam-defining clipper 1
In carrying out limit beam to X-ray, condenser lens 2 is used to be focused the X-ray after limit beam, so that the X that x-ray source device generates
The irradiation face size of ray can be effectively controlled, and improve the x-ray flux irradiated in unit area, reduce X-ray
Source device normal tissue radiation risk when in use improves radiotherapy efficiency.
In order to realize that radiotherapy x-ray source 3, beam-defining clipper 1 and condenser lens 2 are coaxial and successively interval is arranged, x-ray source
Device further includes shell (not shown).In Fig. 1, the section shape of radiotherapy x-ray source 3, beam-defining clipper 1 and condenser lens 2
Shape is circle, therefore shell is preferably arranged to cylindrical housings, radiotherapy x-ray source 3, limit beam in x-ray source device
Device 1 and condenser lens 2 are coaxial and are successively arranged at intervals in shell.The specific structure of shell can be carried out according to actual size
Design, details are not described herein for specific structure, as long as it is same to be able to achieve carrying radiotherapy x-ray source 3, beam-defining clipper 1 and condenser lens 2
Axis and it is successively spaced setting structure, is within the scope of the invention.
Specifically, as shown in Fig. 2, radiotherapy x-ray source 3 is saturating including substrate 31, cold cathode electron emission source 32, anode
It shoots at the target 33 and filter 34, wherein it is preferred that multiple cold cathode electron emission sources 32 are arranged on substrate 31 in array, i.e., it is multiple cold
Cathode electronics emission source 32 forms a kind of face formation formula；Anode transmission target 33 and 32 face of cold cathode electron emission source are arranged, and
It is arranged between substrate 31 and filter 34；Electric field can be applied between anode transmission target 33 and substrate 31, electric field is from substrate 31
It is formed towards 33 direction of anode transmission target, the electron beam that cold cathode electron emission source 32 is launched, under the action of electric field, electronics
Beam bombards anode transmission target 33.Beam bombardment anode transmission target 33, by bremstrahlen, the X-ray of generation, by filter 34
It is filtered, the X-ray of low energy can be absorbed, so that the quality of the X-ray generated from radiotherapy x-ray source 3 is more preferably, lead to
Control anode transmission target 33 and 31 spacing distance of substrate are crossed, i.e., electric field strength between control cathode and anode realizes control electronics
Emission effciency, and then x-ray flux is controlled, while increasing 32 area of cold cathode electron emission source and can also be improved X-ray emission
Efficiency.Meanwhile being generated to guarantee that radiotherapy x-ray source 3 is stablized, X-ray is needed substrate 31, cold cathode electron emission source
32, anode transmission target 33 and filter 34 are encapsulated in vacuum cavity.Due to providing the device of electron beam as cold cathode electron hair
Source 32 is penetrated, and there is no hot cathode in the prior art is used, cold cathode electron emission source 32 does not need to be preheated, and reduction is put
Treatment x-ray source power consumption is penetrated, while anode uses transmission target structure, so that entire x-ray source device space occupied is smaller, structure
It is more compact.
Specifically, the main function of substrate 31 is to provide substrate for cold cathode electron emission source 32, while providing conductive Jie
Matter, does not limit the structure of substrate 31 specifically herein, and preferred substrate 31 is made of ITO conducting glass material or metal material.?
In the present embodiment, multiple cold cathode electron emission sources 32 are arranged in array on substrate 31, by controlling the cold yin integrally arranged
Electron emission source 32 effective area in pole is realized to X-ray emission control from view of profit.Each cold cathode electron emission source 32 can issue
Electronics.The present invention does not limit quantity and arrangement mode of multiple cold cathode electron emission sources 32 on substrate 31.Further
Ground, preferably cold cathode electron emission source 32 are made of field electron emission materials such as carbon nanotube, zinc oxide nanowires.
Specifically, anode transmission target 33 is arranged between substrate 31 and filter 34, and anode transmission target 33 and substrate 31 add
After high pressure, strong electrical field is formed between substrate 31 and anode transmission target 33, so that runaway electron on cold cathode electron emission source 32,
And high-velocity electron beam is formed under strong electrical field acceleration, and bombard anode transmission target 33, by bremstrahlen, generates X and penetrate
Line, does not limit the structure of anode transmission target 33 specifically herein, and preferred anodes transmission target 33 is made of tungsten or metal molybdenum.
Further, in order to form electric field, radiotherapy x-ray source 3 further includes power supply module (not shown).Power supply
Component is electrically connected with substrate 31 and anode transmission target 33 respectively, and power supply module applies anode high voltage electricity on anode transmission target 33,
Substrate 31 and power supply module altogether, are formed from substrate 31 towards the electric field in 33 direction of anode transmission target.The voltage of electric field is preferably protected
10kV-60kV is protected, the selection of specific voltage can treat intensity according to actual radiation and choose.The X generated under 10kV-60kV voltage
Ray is more applicable for X-ray contact treatment.The present invention does not limit the specific structure of power supply module specifically, as long as passing through
Make the structure for generating electric field between substrate 31 and anode transmission target 33, is within the scope of the invention.
Specifically, the main function of filter 34 is the X-ray for absorbing low energy, so that being emitted from radiotherapy x-ray source
X-ray quality more preferably.The flaky structure of preferred filters 34, by the material of the low atomic density such as metallic aluminium or metallic beryllium
It is made.
Further, it in order to realize that substrate 31, anode transmission target 33 and filter 34 are coaxial and successively interval is arranged, radiates
Treating x-ray source 3 further includes vacuum cavity (not shown), and the inside of shell is arranged in vacuum cavity.Substrate 31 in Fig. 2,
The cross sectional shape of anode transmission target 33 and filter 34 is circle, therefore vacuum cavity is preferably arranged to cylindrical body, substrate
31, anode transmission target 33 and filter 34 are coaxial and are successively arranged at intervals in cavity.
In order to guarantee that radiotherapy x-ray source 3 can stablize generation X-ray, preferably need radiotherapy x-ray source 3
Each functional parts between carry out Vacuum Package.And the setting of vacuum cavity, so that it may form this sealed environment, be formed
The specific structure of vacuum cavity can refer to traditional radiation therapy x-ray source glass bulb packaging technology, i.e., in (the cold yin of substrate 31
Pole electron emission source 32), after anode transmission target 33 and filter 34 adjust in the position of vacuum cavity, and draw substrate 31
And 33 high-voltage terminal of anode transmission target, entire vacuum cavity is subjected to Vacuum Package.The specific structure of vacuum cavity, Ke Yigen
It is designed according to actual size, details are not described herein for specific structure, as long as being able to achieve carrying substrate 31, anode transmission target 33 and mistake
Filter 34 and the structure for guaranteeing vacuum environment, are within the scope of the invention.
Further, the flux of X-ray mainly with arranged below related, effective hair including cold cathode electron emission source 32
Area is penetrated, the electric field strength between substrate 31 (cold cathode electron emission source 32) and anode transmission target 33, and limit beam are loaded
Device 1 and the X-rays of 2 pairs of condenser lens outgoing limit Shu great little and focusing multiple are related, can be effective by the above parameter regulation
Control radiotherapy X-ray flux and irradiated area size, realize optimum therapeuticing effect.
Specifically, X-ray emission efficiency can be improved in the effective emission area for increasing cold cathode electron emission source 32, improves
X-ray flux, but emission area is excessive higher to the requirement of rear end focus device, therefore to 31 face of substrate of growth cold-cathode material
Product can not arbitrarily increase, due to the area of substrate 31 it is excessive after, the condenser lens 2 of rear end is required it is higher, therefore can root
According to the size of actual conditions adjustment substrate 31.
The electric field strength between substrate 31 (cold cathode electron emission source 32) and anode transmission target 33 is loaded, with high pressure group
Interval of the part load between the voltage swing and substrate 31 and anode transmission target 33 between substrate 31 and anode transmission target 33
Distance dependent.Smaller when being spaced between substrate 31 and anode transmission target 33, field strength is bigger, what cold cathode electron emission source 32 escaped
Electronics is more, and X-ray emission efficiency is higher, but reduces cold-cathode material and the progress of anode transmission target on substrate with interval
The probability of sparking is higher, it is therefore desirable to adjust the interval between substrate 31 and anode transmission target 33 according to actual needs；High pressure group
Voltage of the part load between substrate 31 and anode transmission target 33 is bigger, and field strength is bigger, and same X-ray emission efficiency is higher, but
It is the rising with voltage, the X-ray energy of outgoing is higher, and penetrating capacity is stronger, therefore needs in radiotherapy according to reality
Border depth of shine controls voltage of the load between substrate 31 and anode transmission target 33.
Further, the X-ray emitted from radiotherapy x-ray source 3, tapered misconvergence of beams need to dissipate biggish
Partial x-ray carries out shielding blocking by 1 pair of beam-defining clipper, to form the relatively uniform X-ray beam of exit direction.Can preferably it exist
Regulating member is set on shell, to adjust the gap between radiotherapy x-ray source 3 and beam-defining clipper 1, limits the X-ray of outgoing
Beam, and then control the flux of X-ray.
Further, on the shell, radiotherapy x-ray source 3, beam-defining clipper 1 and condenser lens 2 can be dismantled individually
Installation, replaces the radiotherapy x-ray source 3 of different x-ray emission effciency, and then can control the therapeutic agent in the unit time
Amount, replacing the different condenser lenses 2 for focusing multiple can control treatment irradiated area, i.e. dosage and disease according to needed for actual therapeutic
Become tissue size to be configured, reaches optimum therapeuticing effect.
X-ray source device proposed by the present invention, compared with prior art, low in energy consumption, irradiated area is small, generates X-ray effect
Rate is high, occupies little space.
Note that the above is only a better embodiment of the present invention and the applied technical principle.It will be appreciated by those skilled in the art that
The present invention is not limited to specific embodiments here, be able to carry out for a person skilled in the art it is various it is apparent variation, again
Adjustment and substitution are without departing from protection scope of the present invention.Therefore, although by above embodiments to the present invention carried out compared with
For detailed description, but the present invention is not limited to the above embodiments only, without departing from the inventive concept, can be with
Including more other equivalent embodiments, and the scope of the invention is determined by the scope of the appended claims.
Claims (11)
1. a kind of radiotherapy x-ray source, which is characterized in that radiotherapy x-ray source (3) includes:
Substrate (31)；
Cold cathode electron emission source (32) is arranged on the substrate (31)；
Anode transmission target (33) is arranged with cold cathode electron emission source (32) face, anode transmission target (33) and the lining
Bottom can apply electric field between (31)；
The side in the anode transmission target (33) backwards to the cold cathode electron emission source (32) is arranged in filter (34)；
The substrate (31), cold cathode electron emission source (32), anode transmission target (33) and filter (34) are encapsulated in vacuum chamber
In body.
2. radiotherapy x-ray source according to claim 1, which is characterized in that the substrate (31) and the anode are saturating
The gap shot at the target between (33) is adjustable.
3. radiotherapy x-ray source according to claim 1, the cold cathode electron emission source (32) is multiple, array
Formula is arranged on the substrate (31).
4. radiotherapy x-ray source according to claim 1, the cold cathode electron emission source (32) by carbon nanotube or
Zinc-oxide nano wire material is made.
5. radiotherapy x-ray source according to claim 1, the substrate (31) is by ITO conducting glass material or gold
Belong to material to be made.
6. radiotherapy x-ray source according to claim 1, the anode transmission target (33) and the filter (34) are equal
Flaky structure, the anode transmission target (33) and the filter (34) are made of metal material.
7. radiotherapy x-ray source according to claim 6, the anode transmission target (33) is by tungsten or metal molybdenum system
At；The filter (34) is made of metallic aluminium or metallic beryllium.
8. radiotherapy x-ray source according to claim 1, which is characterized in that the radiotherapy x-ray source (3) is also
Including power supply module, the power supply module is electrically connected with the substrate (31) and the anode transmission target (33) respectively；The electricity
Source component applies cathode high voltage electricity towards one end of the anode transmission target (33) in the substrate (31) and is grounded, the power supply
Component applies anode high voltage electricity towards one end of the substrate (31) in the anode transmission target (33).
9. radiotherapy x-ray source according to claim 8, which is characterized in that the substrate (31) and the anode are saturating
The voltage applied between (33) of shooting at the target is 10kV-60kV.
10. a kind of x-ray source device, including radiotherapy x-ray source and positioned at the exit end of the radiotherapy x-ray source
Beam-defining clipper (1), which is characterized in that the radiotherapy x-ray source uses radiotherapy X as claimed in one of claims 1 to 9
Radiographic source (3) further includes condenser lens (2), and the condenser lens (2) is located at the beam-defining clipper (1) backwards to the radiotherapy X
One end of radiographic source (3).
11. x-ray source device according to claim 10, the x-ray source device further includes shell, the radiotherapy X
Gap between radiographic source (3) and the beam-defining clipper (1) is adjustable.
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| Application Number | Priority Date | Filing Date | Title |
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| CN201811437049.8A CN109524284A (en) | 2018-11-28 | 2018-11-28 | A kind of radiotherapy x-ray source and x-ray source device |
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| CN201811437049.8A CN109524284A (en) | 2018-11-28 | 2018-11-28 | A kind of radiotherapy x-ray source and x-ray source device |
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Cited By (1)
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| CN112683937A (en) * | 2019-10-18 | 2021-04-20 | 北航（四川）西部国际创新港科技有限公司 | Multi-source ray integration device |
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Application publication date: 20190326 |