CN107432992B - Proximal treatment apparatus and its radioactive source - Google Patents
Proximal treatment apparatus and its radioactive source Download PDFInfo
- Publication number
- CN107432992B CN107432992B CN201610357520.7A CN201610357520A CN107432992B CN 107432992 B CN107432992 B CN 107432992B CN 201610357520 A CN201610357520 A CN 201610357520A CN 107432992 B CN107432992 B CN 107432992B
- Authority
- CN
- China
- Prior art keywords
- treatment apparatus
- radioactive source
- electron beam
- proximal treatment
- anode
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N5/1007—Arrangements or means for the introduction of sources into the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1048—Monitoring, verifying, controlling systems and methods
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N2005/1019—Sources therefor
- A61N2005/1022—Generators, e.g. X-ray tubes
Landscapes
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Pathology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Radiation-Therapy Devices (AREA)
Abstract
A kind of radioactive source of proximal treatment apparatus, comprising: a hot cathode is heated to generate free electron, the free electron by an accelerating field effect and one target element of directive and form an electron beam；One concentrating element partially surrounds the hot cathode, and has a focusing electric field, and the electron beam reduces its diameter by the focusing electric field；One anode tubing string is configured in the inner cavity for entering a lesion or an applicator；The target element is hit by the electron beam positioned at the end of the anode tubing string and generates radiation；And one control mould group, be configured to control the focusing electric field of the concentrating element, so as to adjust the diameter of the electron beam.
Description
Technical field
The present invention is about a kind of proximal treatment apparatus, espespecially a kind of radioactive source of proximal treatment apparatus.
Background technique
Proximal treatment (brachytherapy) is also referred to as close-range treatment or brachytherapy, is a kind of radiation therapy method,
Its by radioactive source be placed in part interior in need for the treatment of or near.Proximal treatment is widely used in cervix cancer, prostate
Cancer, breast cancer, cutaneum carcinoma and brain tumor are applied equally to the oncotherapy at many other positions.Proximal end radiotherapy can be independent
It carries out or is combined with other therapies, such as surgical operation, external exposure radiation and chemotherapy.
Different from external -bean radiation therapy, the X-ray of high-energy is from extracorporeal irradiation tumour.Proximal treatment is by radioactive source standard
Really it is placed in the lesion region of cancer or tumour.The feature of proximal treatment maximum is: irradiation affects only ten around radioactive source
Point limited region so that tumour receives the irradiation of high dose, and apart from radioactive source it is farther away arround normal tissue irradiated
To dosage can quickly reduce.In addition, over the course for the treatment of, if patient or intracorporal tumour move, radioactive source is also
It is able to maintain the correct position relative to tumour.These characteristics of close-range treatment make it have external exposure be unable to reach it is a variety of excellent
Point: tumour can receive topical high-dose treatment, while the health tissues unnecessary damage obtained of surrounding is also dropped significantly
It is low.
Compared with other radiation therapy technologies, the course for the treatment of of proximal treatment is shorter, helps to reduce and deposit in treatment gap every time
The probability of cancer cell division and growth living.Compared with external radiotherapy, patient can reduce the number for carrying out institute's medical treatment.Treatment is usual
It is to be carried out in the form of outpatient service, provides more direct, mode of easily seeing a doctor for patient.These features of close-range treatment are protected
Most patients have been demonstrate,proved to the good tolerance of brachytherapy.Brachytherapy can effectively treat a plurality of types of cancers.It controls
Treat the result shows that, the cure rate of close-range treatment is close with operation or external exposure.When these technologies combine, cure rate is more
It is high.In addition, the risk that close-range treatment generates side effect is lower.
In proximal treatment program, the intracorporal applicator of people (applicator) is first usually placed in the confirmation of X image
Behind position, then radioactive source is automatically imported via machine conduit to the correct position of predetermined treatment and is stayed for some time to predetermined
Dosage.However in order to enable tumour receives enough treatment exposure doses, but normal tissue arround not influencing or injuring,
The exposure dose of the radioactive source must be exactly accurate, however traditional radioactive source but can not often generate accurate radiological agent
Amount.In addition to this, the radioactive source of traditional proximal treatment apparatus is usually reflective, i.e., when electron beam is hit to anode after institute
The radiation direction of generation is by reflection (i.e. different from the direction that electron beam carries out), the radioactive source of reflective proximal treatment apparatus
Light-emitting angle is small and only generates 1% radiation, and 99% energy is converted to thermal energy, and energy converts inefficiency, can control to reach
The radiological dose of tumour is treated, bigger input power need to be used, it is opposite to be also required to the radiator that more thermal energy are taken away, therefore
Single unit system can not be miniaturized.Therefore precise radiation dosage can be generated and there is high-energy to convert efficiency by being bound to develop
Proximal treatment apparatus or proximal treatment apparatus radioactive source.
Summary of the invention
The purpose of the present invention is that efficiency can be converted with accuracy controlling radiological dose and with high-energy by providing one kind
The radioactive source of proximal treatment apparatus, comprising:
One cathode assembly is configured to one electron beam of transmitting, and includes: a hot cathode, is heated to generate free electricity
Son, the free electron by an accelerating field effect and one anode assemblies of directive and form an electron beam；One concentrating element, portion
Divide and surround the hot cathode, and there is a focusing electric field, the electron beam reduces its diameter by the focusing electric field；
The anode assemblies are configured to receive the electron beam and generate radiation, and include: an anode tubing string, quilt
Construction with contact or into a lesion or enter an applicator inner cavity in；One target element, positioned at the anode tubing string
End is hit by the electron beam and generates the radiation；
One power supply is configured to drive the hot cathode and generates the free electron, provide be biased in the concentrating element and
Generate the focusing electric field, and provide voltage in the cathode assembly and the anode assemblies with the cathode assembly with
The accelerating field is generated between the anode assemblies；
One shell is constructed so that the cathode assembly and anode assemblies insulate；And
One control mould group, is configured to the bias that control is applied on the concentrating element, to adjust the focusing
The focusing electric field of element, so as to adjust the diameter of the electron beam.
In one embodiment of this invention, radiation caused by the target element is directed through the target element, and without warp
Cross reflection.
In one embodiment of this invention, the control mould group is also configured to control the pipe electricity that the power supply is driven
The voltage of stream or the accelerating field.
In one embodiment of this invention, the cathode assembly and anode assemblies are respectively at the both ends of the shell.
In one embodiment of this invention, the concentrating element is a cup configuration, basin type structure or tubular column shape structure.
In one embodiment of this invention, the material of the target element is gold.
In one embodiment of this invention, the range of a tube current of the electron beam between 40-60uA, it is described partially
The range of pressure is between 0-300V or the range of the accelerating field is between 40-60kV.
In one embodiment of this invention, the material of the end of the anode tubing string is a transparent material of radiation.
In one embodiment of this invention, the material of the shell is ceramics.
In one embodiment of this invention, the hot cathode is a tungsten wire.
The purpose of the present invention is that efficiency can be converted with accuracy controlling radiological dose and with high-energy by providing one kind
A kind of proximal treatment apparatus of the radioactive source of proximal treatment apparatus, comprising:
One applicator is configured to contact with a lesion；And
One radioactive source is configured to generate radiation comprising:
One cathode assembly is configured to one electron beam of transmitting, and includes: a hot cathode, is heated to generate free electricity
Son, the free electron by an accelerating field effect and one anode assemblies of directive and form an electron beam；One concentrating element, portion
Divide and surround the hot cathode, and there is a focusing electric field, the electron beam reduces its diameter by the focusing electric field；
The anode assemblies are configured to receive the electron beam and generate radiation, and include: an anode tubing string, quilt
Construction with contact or into a lesion or enter an applicator inner cavity in；One target element, positioned at the anode tubing string
End is hit by the electron beam and generates the radiation；
One power supply is configured to drive the hot cathode and generates the free electron, provide be biased in the concentrating element and
The focusing electric field is generated, and provides voltage in the cathode assembly and the anode assemblies in the cathode assembly and institute
It states and generates the accelerating field between anode assemblies；
One shell is constructed so that the cathode assembly and anode assemblies insulate；And
One control mould group, is configured to the bias that control is applied on the concentrating element, to adjust the focusing
The focusing electric field of element, so as to adjust the diameter of the electron beam.
In one embodiment of this invention, radiation caused by the target element is directed through the target element, and without warp
Cross reflection.
In one embodiment of this invention, the control mould group is also configured to control the pipe electricity that the power supply is driven
The voltage of stream or the accelerating field.
In one embodiment of this invention, the cathode assembly and anode assemblies are respectively at the both ends of the shell.
In one embodiment of this invention, the concentrating element is a cup configuration, basin type structure or tubular column shape structure.
In one embodiment of this invention, the material of the target element is gold.
In one embodiment of this invention, the range of a tube current of the electron beam between 40-60uA, it is described partially
The range of pressure is between 0-300V or the range of the accelerating field is between 40-60kV.
In one embodiment of this invention, the material of the end of the anode tubing string is a transparent material of radiation.
In one embodiment of this invention, the material of the shell is ceramics.
In one embodiment of this invention, the hot cathode is a tungsten wire.
The radioactive source of proximal treatment apparatus of the invention is biased in the concentrating element by offer and generates the focusing
Electric field, and the bias that control is applied on the concentrating element, to adjust the focusing electric field of the concentrating element, thus
Adjust the diameter of the electron beam.When the bias is larger, the diameter of the electron beam is smaller, described to be located at the sun
The area that the target element of the end of pole pipe column is hit by electron beam is smaller, and generated radiological dose is lower；When the bias compared with
Hour, the electron beam is relatively large in diameter, the face that the target element of the end positioned at the anode tubing string is hit by electron beam
Product is larger, and generated radiological dose is higher, the radiological dose that accuracy controlling lock generates in this way.
In addition to this, the radioactive source of proximal treatment apparatus of the invention is penetration, and electron beam hits the target element, institute
The radiation of generation is directed through the target element, and have without reflection, therefore in input energy 99% for generate radiate, only
1% energy conversion is thermal energy, therefore smaller power can be used to can reach higher radiological dose output, need not also increase additional heat dissipation
Proximal treatment apparatus of the invention is miniaturized in device.
Detailed description of the invention
In Fig. 1 system embodiment according to the present invention, an element relation schematic diagram of the radioactive source of a proximal treatment apparatus；
In Fig. 2 system embodiment according to the present invention, a structural schematic diagram of the radioactive source of a proximal treatment apparatus；
In Fig. 3 embodiment according to the present invention, a schematic illustration of the radioactive source of a proximal treatment apparatus；And
In Fig. 4 embodiment according to the present invention, the beam diameter measurement experiment of the radioactive source of a proximal treatment apparatus
A schematic diagram.
Specific embodiment
Fig. 1 and Fig. 2 are please referred to, is respectively the radioactive source of a proximal treatment apparatus in an embodiment according to the present invention
An element relation schematic diagram and structural schematic diagram.The proximal treatment apparatus (brachytherapy apparatus)
Radioactive source 1 (radiation source) is for generating radiation (radiation) comprising 10 (cathode of a cathode assembly
Assembly), an anode assemblies 20 (anode assembly), a power supply 30 (power source), a shell 40
(housing) and one controls mould group 50 (control module).
The cathode assembly 10, for emitting an electron beam, and including a cathode 11 (cathode) and a concentrating element
12(focusing element).The cathode 11 can be the heat that free electron is produced under the excitation for being heated high temperature
Cathode 11 (hot cathode), such as a heated filament 11 (hot filament), or by the excitation of visible light or black light
The cathode of the lower photocathode (photo cathode) for generating free electron or any other type.Preferably of the invention one
Embodiment in, use heated filament 11 as the cathode, material can selected from containing barium compound, containing strontium compound, contain yttrium
At least one of group composed by compound and Tungstenic compound.In the preferred embodiment of the present invention, using tungsten
Silk is as the heated filament.The free electron under the action of accelerating field of a high pressure and anode assemblies 20 described in directive and shape
At an electron beam, it is positive potential in anode, and can be between 1kV extremely that the accelerating field of the high pressure, which is negative potential in cathode,
Range between 100kV, in the preferred embodiment of the present invention, the accelerating field is between 40kV to the model between 60kV
It encloses.12 part of concentrating element surrounds the cathode 11, and shape is a hollow shape, at least has opening, example in one end
Such as a cup type, basin type are one tubular, and in an embodiment of the present invention, the concentrating element 12 is a cup type, the cathode 11
It is placed in the inner space of the concentrating element 12, opening of the electron beam that the cathode 11 is emitted from the concentrating element 12
Pass through.The concentrating element 12 generates a focusing electric field with negative potential under the action of a bias.When the electron beam is logical
When crossing the concentrating element 12, the focusing electric field reduces beam diameter.Above-described cathode (or hot cathode) 11 with it is poly-
The material or shape of burnt element 12, only implementation example, the cathode 11 of the radioactive source of proximal treatment apparatus of the invention are suitable for
Various material and concentrating element 12 are suitable for various shapes, therefore application range of the invention should not be limited with this.
The anode assemblies 20 generate radiation for receiving the electron beam, and including an anode tubing string 22
(anode tube) and target element 21 (target element).The anode tubing string is an elongate tubular member, described
Electron beam is used for into the inner cavity of an applicator or one lesion of entrance or contact, such as one swollen by wherein
In tumor or malignant tissue.The target element is excited positioned at the end of the anode tubing string when being hit by the electron beam
And generate the radiation.In the preferred embodiment of the present invention, radiation caused by the target element is directed through the target
Element, and without reflection.For example, the very thin thickness of the target element is for example, coated on anode tubing string end
Lumen on the inside of a coating, material can be tantalum, platinum and gold, in the preferred embodiment of the present invention, the target element
The material of coating is gold.And the material of the end of the anode tubing string is the transparent material of radiation, such as glass.Therefore this hair
Have in the input energy of bright proximal treatment apparatus 99% for generate radiation, only 1% energy conversion is thermal energy, thus it is usable compared with
Small-power can reach higher radiological dose output.If the thickness of target element is too thick, radiation can not be directed through the target element,
The mode for having to pass through reflection changes radiation direction (i.e. different from the direction that electron beam carries out), can make the radiation of described device
Source light-emitting angle is small and only generates 1% radiation, and 99% energy is converted to thermal energy, and energy converts inefficiency.
The power supply 30 passes through a pair of of feedthrough lead 31 and provides energy to heat the hot cathode 11, drives described in its generation
Free electron.The power supply 30 simultaneously provides high voltage in the cathode assembly 10 and the anode assemblies 20, in the cathode
The accelerating field is generated between component 10 and the anode assemblies 20.Effect of the free electron in the accelerating field of the high pressure
Anode assemblies 20 described in lower and directive and form electron beam, the accelerating field is negative potential in cathode, is positive potential in anode.
For example, the accelerating field of the high pressure can be between 1kV to the range between 100kV, and the tube current of the electron beam
It can be between 1uA to the range between 100uA.In the preferred embodiment of the present invention, the accelerating field between 40kV extremely
Range between 60kV, and the tube current of the electron beam can be between 40uA to the range between 60uA.In addition to this, described
Power supply 30, which also provides, to be biased in the concentrating element 12 and generates the focusing electric field for having negative potential, so that the electronics
When beam passes through the concentrating element 12, the focusing electric field reduces beam diameter.In one embodiment of this invention, described inclined
Range of the range of pressure between 0-300V.The voltage of accelerating field described above, the bias of focusing electric field and tube current
Range, only implementation example, the radioactive source of proximal treatment apparatus of the invention be suitable for multiple voltage and current range, therefore
Application range of the invention should not be limited with this.
The shell 40 is constructed so that the cathode assembly 10 and anode assemblies 20 insulate, due to the cathode assembly 10
Potential difference between anode assemblies 20 is very high (between 1kV to the range between 100kV), therefore whether the shell can
Really it is critically important for so that the cathode assembly 10 is insulated with anode assemblies 20.In the preferred embodiment of the present invention, described
Cathode assembly 10 and anode assemblies 20 respectively at the both ends of the shell and the material of the shell 40 is ceramics.It is above-described
The material of shell 40, only one implements example, and the shell of the radioactive source of proximal treatment apparatus of the invention is suitable for various material,
Therefore application range of the invention should not be limited with this.
The control mould group 50 is configured to the bias that control is applied on the concentrating element 12, described in adjustment
The focusing electric field of concentrating element 12, so as to adjust the diameter of the electron beam, to adjust generated radiological dose.See
Fig. 3, for according in one embodiment of the invention, a schematic illustration of the radioactive source 1 of a proximal treatment apparatus.When described inclined
The diameter of (above) when pressing larger, the electron beam is smaller, 21 quilt of target element of the above-mentioned end positioned at the anode tubing string 22
The area that electron beam is hit is smaller, and generated radiological dose is lower；When the bias is smaller (following figure), the electron beam
It is relatively large in diameter, the area that the target element 21 of the above-mentioned end positioned at the anode tubing string 22 is hit by electron beam is larger, produced
Radiological dose it is higher, in this way accuracy controlling lock generate radiological dose.
In another preferred embodiment of the invention, the control mould group not only can control and be applied to the focusing member
The bias on part can also control the tube current that the power supply is driven, so as to adjust the density of the electron beam.Work as institute
The density for stating electron beam is larger, and generated radiological dose is higher；When the density of the electron beam is smaller, generated radiological agent
Measure lower (figure is not shown).By controlling the bias and the tube current simultaneously more accurately to adjust generated put
Penetrate dosage.
Proximal treatment apparatus of the invention, including an applicator (applicator) and above-mentioned radioactive source 1.It is described to apply
It being configured to contact with a lesion with device, shape is suitable for being bonded with lesion, or the lesion of covering large area, or
The body cavity being located at lesion, or traction lesion etc. are strutted, so that lesion can be close to the target element for generating radiation
21.For example, the applicator can for elongate tubular, sacculus shape, dish type, cupuliform, multi-pipe shape, more balloon types or taper etc.,
Or the combination of the above shape.The end of the anode tubing string 22 of the radioactive source 1 and target element 21 are inserted into the applicator
Among, to be located close to by the applicator in lesion.The shape of above-described applicator, only implementation example, this hair
Bright proximal treatment apparatus is suitable for various applicators, therefore application range of the invention should not be limited with this.
The diameter of electron beam with the naked eye can not be observed directly, but its diameter can be measured via round-about way.Please
With reference to Fig. 4, for according in one embodiment of the invention, the beam diameter of the radioactive source 1 of a proximal treatment apparatus measures real
The schematic diagram tested.A photosensitive screen 100 is placed at 50 centimeters of the end of the radioactive source 1 apart from the proximal treatment apparatus,
To sense radiation caused by the target element 21 of the radioactive source 1, in the end of the photosensitive screen 100 and the radioactive source 1
Between a specific position place the tungsten ball 200 (tungsten bead) of 5 millimeters of a diameter, the tungsten ball can stop described put
Radiation caused by the target element 21 in source is penetrated, so that the photosensitive screen 100 generates one without photosensitive hot spot 300.Work as electron beam
Diameter is bigger, and the confusion region 301 of generated 300 diameter of hot spot and hot spot outer rim also can be bigger, when beam diameter is smaller, institute
300 diameter of hot spot of generation and the confusion region 301 of hot spot outer rim then can be smaller.300 diameter of hot spot and hot spot outer rim can be passed through
Confusion region 301 calculate, actual beam width.Please refer to the following table 1, be beam diameter measurement experiment as a result,
It is shown under each bias the size and its corresponding equivalent dose of (1-300V) institute beam hot spot 300, uses three in this experiment
It repeats, respectively using the radioactive source of the different proximal treatment apparatus of three with same size according to the present invention.From table 1
As can be seen that the diameter of hot spot is smaller, represents the diameter that the focusing electric field reduces electron beam really, makes when bias is higher
It obtains the area that the target element 21 is hit by electron beam to reduce, and generates lower dosage；It is opposite, when bias is lower, hot spot
Diameter and electron beam diameter it is also bigger, and generate higher dosage.In addition, three repeat the spot size under identical bias
Difference between equivalent dose is little, it may thus be appreciated that being a kind of adjust accurately using bias (or focusing electric field) adjustment radiological dose
Reliable method.Above-described experimental result only indicates that the radioactive source of proximal treatment apparatus of the invention is applied to
When the effect of, therefore application range of the invention should not be limited with this experimental result.
Table 1:
Those skilled in the art when implementing pattern institute it can be appreciated that without prejudice under spirit of that invention according to the present invention
The various change that can be carried out.Therefore, obvious listed state sample implementation is not intended to limit the invention, but is attempted in appended right
Under the definition of claim, it is covered by modification done in spirit and scope of the invention.
Claims (10)
1. a kind of radioactive source of proximal treatment apparatus, it is characterised in that: the radioactive source of the proximal treatment apparatus includes:
One cathode assembly is configured to one electron beam of transmitting, and includes:
One hot cathode is heated to generate free electron, the free electron by an accelerating field effect and one anode of directive
Component and form an electron beam；
One concentrating element partially surrounds the hot cathode, and has a focusing electric field, and the electron beam passes through the focusing electric field
And reduce the diameter of the electron beam；
The anode assemblies are configured to receive the electron beam and generate radiation, and include:
One anode tubing string is configured to contact or enter a lesion or enter in the inner cavity of an applicator；
One target element is hit by the electron beam positioned at the end of the anode tubing string and generates the radiation；
One power supply is configured to drive the hot cathode and generates the free electron, provides and is biased in the concentrating element and generates
The focusing electric field, and voltage is provided in the cathode assembly and the anode assemblies in the cathode assembly and the sun
The accelerating field is generated between the component of pole；
One shell is constructed so that the cathode assembly and anode assemblies insulate；And
One control mould group, is configured to the bias that control is applied on the concentrating element, to adjust the concentrating element
Focusing electric field, so as to adjust the diameter of the electron beam.
2. the radioactive source of proximal treatment apparatus as described in claim 1, it is characterised in that: radiation caused by the target element
It is directed through the target element, and without by reflecting.
3. the radioactive source of proximal treatment apparatus as described in claim 1, it is characterised in that: the control mould group is configured to control
Make the voltage of the tube current that the power supply is driven or the accelerating field.
4. the radioactive source of proximal treatment apparatus as described in claim 1, it is characterised in that: the cathode assembly and anode assemblies
Respectively at the both ends of the shell.
5. the radioactive source of proximal treatment apparatus as described in claim 1, it is characterised in that: the concentrating element is a cup type knot
Structure, basin type structure or tubular column shape structure.
6. the radioactive source of proximal treatment apparatus as described in claim 1, it is characterised in that: the material of the target element is gold.
7. the radioactive source of proximal treatment apparatus as described in claim 1, it is characterised in that: a tube current of the electron beam
Range between 40uA between 60uA or the range of the bias between 0V between 300V or the range of the accelerating field
Between 40kV between 60kV.
8. the radioactive source of proximal treatment apparatus as described in claim 1, it is characterised in that: the material of the end of the anode tubing string
Matter is a transparent material of radiation.
9. the radioactive source of proximal treatment apparatus as described in claim 1, it is characterised in that: the material of the shell is ceramics.
10. the radioactive source of proximal treatment apparatus as described in claim 1, it is characterised in that: the hot cathode is a tungsten wire.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610357520.7A CN107432992B (en) | 2016-05-26 | 2016-05-26 | Proximal treatment apparatus and its radioactive source |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610357520.7A CN107432992B (en) | 2016-05-26 | 2016-05-26 | Proximal treatment apparatus and its radioactive source |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN107432992A CN107432992A (en) | 2017-12-05 |
| CN107432992B true CN107432992B (en) | 2019-08-13 |
Family
ID=60453095
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201610357520.7A Active CN107432992B (en) | 2016-05-26 | 2016-05-26 | Proximal treatment apparatus and its radioactive source |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN107432992B (en) |
Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109125958B (en) * | 2018-11-05 | 2020-10-16 | 深圳铭杰医疗科技有限公司 | Connecting structure of accelerating tube and beam needle and radiotherapy equipment |
| EP3881896A1 (en) * | 2020-03-18 | 2021-09-22 | RaySearch Laboratories AB | A method of generating a radiotherapy treatment plan, computer program and computer system for generating a radiotherapy treatment plan, and radiotherapy delivery system |
| CN115811999A (en) * | 2020-07-27 | 2023-03-17 | 上海联影医疗科技股份有限公司 | Radiotherapy equipment and microwave source thereof |
| CN115645761B (en) * | 2022-12-28 | 2023-03-28 | 广东省新兴激光等离子体技术研究院 | Tumor radiotherapy equipment and control method thereof |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6134300A (en) * | 1998-11-05 | 2000-10-17 | The Regents Of The University Of California | Miniature x-ray source |
| CN1596140A (en) * | 2001-06-19 | 2005-03-16 | 光电子公司 | Optically driven therapeutic radiation source |
| CN101521135A (en) * | 2009-03-26 | 2009-09-02 | 公安部第一研究所 | Grid-control nanocarbon cathode field emission X-ray pipe |
| KR20130122249A (en) * | 2012-04-30 | 2013-11-07 | 이화여자대학교 산학협력단 | Super miniature ionization beam tube for epithelial cancer brachytherapy |
| CN104411081A (en) * | 2014-11-13 | 2015-03-11 | 重庆大学 | Linear array micro-nano focus X-ray source for micro-nano CT (computer tomography) system |
| CN105590816A (en) * | 2016-02-02 | 2016-05-18 | 赵文天 | Cold-cathode large-power electron beam gun |
-
2016
- 2016-05-26 CN CN201610357520.7A patent/CN107432992B/en active Active
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6134300A (en) * | 1998-11-05 | 2000-10-17 | The Regents Of The University Of California | Miniature x-ray source |
| CN1596140A (en) * | 2001-06-19 | 2005-03-16 | 光电子公司 | Optically driven therapeutic radiation source |
| CN101521135A (en) * | 2009-03-26 | 2009-09-02 | 公安部第一研究所 | Grid-control nanocarbon cathode field emission X-ray pipe |
| KR20130122249A (en) * | 2012-04-30 | 2013-11-07 | 이화여자대학교 산학협력단 | Super miniature ionization beam tube for epithelial cancer brachytherapy |
| CN104411081A (en) * | 2014-11-13 | 2015-03-11 | 重庆大学 | Linear array micro-nano focus X-ray source for micro-nano CT (computer tomography) system |
| CN105590816A (en) * | 2016-02-02 | 2016-05-18 | 赵文天 | Cold-cathode large-power electron beam gun |
Also Published As
| Publication number | Publication date |
|---|---|
| CN107432992A (en) | 2017-12-05 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US6320932B2 (en) | Miniature radiation source with flexible probe and laser driven thermionic emitter | |
| US6464625B2 (en) | Therapeutic method and apparatus for debilitating or killing microorganisms within the body | |
| JP3110463B2 (en) | X-ray source using shape radiation pattern | |
| KR100255723B1 (en) | Miniaturized low power x-ray source | |
| US8559598B2 (en) | Miniature X-ray source device for effecting radiation therapy | |
| US6556651B1 (en) | Array of miniature radiation sources | |
| CN107432992B (en) | Proximal treatment apparatus and its radioactive source | |
| US20060133575A1 (en) | X-ray needle apparatus and method for radiation treatment | |
| US6728335B1 (en) | Controller for array of miniature radiation sources | |
| CN202715138U (en) | Mobile X-ray unit and applicator cap thereof | |
| US6920202B1 (en) | Therapeutic radiation source with in situ radiation detecting system | |
| CN107335153A (en) | Robot lower energy photon plesioradiotherapy system | |
| JP2004522558A (en) | Device for X-ray therapy | |
| CN109395258A (en) | Precise radiotherapy method and system based on sorghum procyanidins | |
| US20060126789A1 (en) | Catheter with inflatable balloon assembly and optically activated x-ray source | |
| TWI577413B (en) | Brachytherapy apparatus and radiation source thereof | |
| JP4279565B2 (en) | Slender X-ray irradiation tool | |
| US6856668B1 (en) | Method of treating a tumor by pre-irradiation | |
| RU2519772C2 (en) | Method for exposing human body pathologies to radiation and device for implementing same (versions) | |
| EP2850634B1 (en) | Radiotherapy apparatus | |
| RU2238774C2 (en) | Device for applying radiation therapy |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |