CN210092024U

CN210092024U - X-ray bulb tube

Info

Publication number: CN210092024U
Application number: CN201920558746.2U
Authority: CN
Inventors: 陈基炜; 涂彧; 黄圣雁
Original assignee: Kunshan Traditional Chinese Medicine Hospital
Current assignee: Kunshan Traditional Chinese Medicine Hospital
Priority date: 2019-04-23
Filing date: 2019-04-23
Publication date: 2020-02-18
Anticipated expiration: 2029-04-23

Abstract

The utility model discloses an X ray bulb, include: the cathode comprises at least four groups of independently arranged emission units, a plurality of independently controlled emission bodies are arranged in any one emission unit, and the emission units are at least distributed in two planes; the anode is matched with the cathode and comprises a plurality of target bodies matched with the emitter, and the target bodies and the emitter are arranged correspondingly; the target body receives electron-generated X-ray beams emitted from the emitter to perform convergent imaging; a vacuum space, the cathode and the anode both being located within the vacuum space. The utility model discloses can utilize nanometer semiconductor material emission electron to the performance reduction and the restriction of instability to the negative pole of filament after long-term the use among the prior art have been reduced.

Description

X-ray bulb tube

Technical Field

The utility model relates to a medical imaging equipment field, concretely relates to X ray bulb.

Background

X-rays are widely used in CT scanners, and the core component for generating X-rays is an X-ray bulb, which has four main conditions for generating X-rays: 1. the cathode filament is used for enabling current to pass through the filament and heating the filament to enable the filament to overflow electrons; 2. the anode target surface is divided into a fixed anode target surface (with lower power) and a rotating anode target surface (with higher power), the function of the anode target surface is to block electrons so that the electrons collide with the anode target surface to generate X rays, and the anode target surface is made of rhenium, tungsten, rhodium, molybdenum and the like or alloys thereof; 3. the high vacuum environment of the bulb tube has the function that electrons are not blocked in the advancing process, and the anode and cathode metals are not easy to oxidize in the vacuum environment; 4. the high voltage between the cathode and the anode has the function of accelerating electrons overflowing from the filament and providing kinetic energy for the electrons to collide with the target surface of the anode.

In the prior art, two medical X-ray bulb tube filaments are mainly arranged, the two filaments are both arranged in a cathode focusing cup, one filament is a special filament for fluoroscopy, and the current passing through the filament during fluoroscopy is smaller and is generally lower than 5 mA; the other is a filament special for photography, and the passing current is generally 200mA-800mA when in photography. Since the two filaments assume different functions, the number of electrons emitted and the current passing through the filaments are also different.

However, the service life of the filament is shortened when the filament is used excessively for a long time, once the filament is broken, the current cannot form a loop, electrons cannot overflow, so that X-rays cannot be generated, and the filament can only be stopped for maintenance.

SUMMERY OF THE UTILITY MODEL

The to-be-solved technical problem of the utility model is to provide an X ray bulb, its emission unit that can utilize the multiunit independent setting launches the electron.

In order to solve the technical problem, the utility model provides an X-ray bulb, include: the cathode comprises at least four groups of independently arranged emission units, a plurality of independently controlled emission bodies are arranged in any one emission unit, and the emission units are at least distributed in two planes; the anode is matched with the cathode and comprises a plurality of target bodies matched with the emitter, and the target bodies are arranged corresponding to the emitter; the target body receives electron-generated X-ray beams emitted from the emitter to perform convergent imaging; a vacuum space, the cathode and the anode both being located within the vacuum space.

Further, the emitters in any one of the emission units are arranged in a staggered mode.

Furthermore, a plurality of baffles are arranged in any one of the emission units so as to separate the emission units into a plurality of independent compartments; the emitters are correspondingly arranged in the compartment so as to reduce mutual interference among the emitters.

Furthermore, the X-ray bulb tube also comprises a master control module, wherein the master control module comprises a controller, an amplification module and a plurality of emitters which are arranged in parallel; the controller is used for improving the base value current signal, and the amplifying module is used for amplifying the electric signal and transmitting the electric signal to the emitter.

Further, the general control module further comprises a feedback module, the feedback module comprises a plurality of detection elements, and the detection elements are correspondingly arranged in the compartments; the detection element is capable of receiving the numerical ratio of electrons overflowing from the emitter and detecting the numerical ratio by an ammeter.

Further, the master control module further comprises a judging module, and the judging module can judge to increase or decrease the electric signal according to the result of the feedback module; and the controller can adjust the emission unit according to the judgment module so as to distribute the electron quantity of the emission unit.

Further, the total emission tube current of all the emitters is 200mA-800 mA.

Another object of the present invention is to provide a CT scanner comprising an X-ray tube according to any of the claims 1-9.

The utility model has the advantages that:

1. the independently arranged emitters can emit electrons, so that the emitters are used for emitting the electrons to generate X-ray beams, and the X-ray beams are matched with a target body for convergence imaging; therefore, the performance reduction and instability restriction of the filament after long-term use in the prior art on the cathode are reduced, and the use cost and the fault period are reduced; the service life of the cathode can be prolonged, so that the service life of the X-ray bulb tube is prolonged;

2. the cathode comprises at least four groups of independently arranged emission units, and the emission units are distributed in at least two planes, so that the distribution of electrons acting on the target body can be kept uniform by the emission units, and the independently arranged emission units can compensate each other during emission, so that electrons overflowing from the emitter can uniformly act on the anode.

Drawings

Fig. 1 is a schematic diagram of a firing unit and a projectile of the present invention;

fig. 2 is a circuit block diagram of the present invention;

FIG. 3 is a circuit diagram of a feedback module;

FIG. 4 is a schematic diagram of the electron emission distribution in the normal state of the present invention;

FIG. 5 is a schematic diagram of the distribution of electron emission in an abnormal state of the present invention;

fig. 6 is a schematic diagram of the distribution of the adjusted electron emission of the present invention.

The reference numbers in the figures illustrate: 1. a transmitting unit; 2. an emitter; 3. a baffle plate; 4. a detection element.

Detailed Description

The present invention is further described with reference to the following drawings and specific embodiments so that those skilled in the art can better understand the present invention and can implement the present invention, but the embodiments are not to be construed as limiting the present invention.

Referring to fig. 1, an embodiment of an X-ray tube according to the present invention includes a cathode, an anode and a vacuum space, wherein the cathode provides a sufficient number of electrons to obtain a high-speed electron current, and the electrons can generate X-rays when they impinge on the anode cooperating with the cathode; and in order for electrons to be not blocked by gas molecules in high-speed motion and to reduce energy, it is necessary to place the cathode and the anode in a vacuum space.

The cathode comprises at least four groups of emission units 1 which are independently arranged, and the emission units 1 are at least distributed in two planes; a plurality of independently controlled emitters 2 are arranged in the emitting unit 1. The independently arranged transmitting units 1 can mutually compensate by independently controlling independent work so as to reduce the influence on the overall working performance when one group is damaged. All the emission units 1 are distributed in at least two planes, that is, the emission units 1 are arranged in a three-dimensional space structure in the present embodiment, and the emission units 1 in three-dimensional distribution can keep the distribution of the overflowing electrons more uniform, unlike the planar arrangement of the emission units 1. Meanwhile, because the emission units 1 are distributed on at least two planes, emission compensation can be carried out among the emitters 2 arranged in different emission units 1, and the influence on the overall performance when part of the emitters 2 are damaged can be reduced. In this embodiment, five sets of emission units 1 are provided, and the emission units 1 are sequentially arranged in five directions, i.e., up, down, rear, left, and right, of the focusing cup, so that they form a rectangular shape uniformly distributed when they act on the anode. The emitters 2 arranged inside the emission unit 1 are distributed in a staggered manner, which can maintain the uniformity of the distribution of the overflowing electrons with a small number of emitters 2.

The emitter 2 arranged in the emitting unit 1 is controlled independently, and in the starting process of the rotating anode, incident light rays are emitted into a vacuum from a cathode due to the external photoelectric effect, and photoelectrons do accelerated motion in the vacuum under the action of an electric field and are finally received by the anode with high potential. The total emission tube current of all the emitters is 200mA-800mA, wherein alkali metal is selected as the emitter. The emission unit emission electron that utilizes independent setting can effectively alleviate the drawback when utilizing the filament to spill over the electron among the prior art, and the performance of the filament of negative pole filament can reduce after long-time the use, in case the filament fracture can lead to unable return circuit that forms, and then leads to the electron can't spill over. But the service life of the cathode and the service life of the X-ray bulb tube can be prolonged by mutually supplementing a plurality of groups of emission units which are independently arranged.

The anode comprises a plurality of target bodies matched with the emitter 2, and the target bodies are arranged corresponding to the emitter 2 of the cathode. The target is capable of receiving electron-generated X-ray beams that have overflowed the emitter 2 and of converging at the image plane to form an image.

A plurality of baffles 3 are arranged in the emission unit 1, and can divide the emission unit 1 into a plurality of mutually independent compartments. Inside a group of emitter units 1 the number of emitters 2 is equal to the number of compartments, i.e. the emitters 2 are arranged inside the compartments individually and in a one-to-one correspondence. By isolating the emitters 2 from each other by means of compartments, the mutual interference of electrons between the individual emitters 2 can be reduced. Firstly, the baffle 3 can place the electrons overflowing firstly to form an electron cloud in the space, so that space charge effect is caused to interfere the electrons overflowing from other emitters 2; secondly, the baffle 3 can prevent the charges of other units from interfering with the module received by the transmitting unit 1, so as to cause the information error of the feedback module. Because the temperature when the electrons overflow is high, the material of the baffle 3 in this embodiment is glass with high temperature resistance and high strength.

Referring to fig. 2 and 3, the X-ray tube further includes a master control module, the master control module includes a controller, an amplification module, a feedback module and a judgment module, the controller is configured to increase a base current signal and transmit the current signal to the amplification module connected thereto; the amplification module is capable of amplifying the electrical signal and of further transmitting the electrical signal to the emitter 2. The feedback module comprises a number of detection elements 4, which detection elements 4 are arranged in correspondence with the emitters 2 and in the compartment, the detection elements 4 in this embodiment preferably being of a metallic material. The detecting element 4 can receive electrons overflowing from the emitter 2, and the detecting element 4 is connected with an ammeter which can judge the current in the corresponding compartment by using the connected ammeter and can judge the number of electrons overflowing from the emitter according to the detected current. The feedback module comprises a detection element 4, an ammeter and a protection resistor, wherein the detection element 4 is arranged in the compartment and corresponds to the emitter. The detection element 4 is electrically connected to the ammeter and the protection resistor in turn, and has its end grounded. The judging module is arranged between the feedback module and the controller, and can judge the relationship between the current amount received by all the detecting elements 4 and the total current amount according to the result of the feedback module and judge whether the electric signal needs to be increased or decreased. When the number of electrons received by all the detecting elements 4 is smaller than the total emission amount, the controller can specifically allocate the number of electrons overflowing from each emitting unit 1 according to the working state of each group of emitting units 1, so as to ensure good performance of the X-ray tube during working.

After the total control module is used for distributing the electrons overflowing from the emitter, the feedback module is short-circuited, so that the electrons overflowing from the cathode can shoot on the target body of the anode.

Referring to fig. 4 to 6, the mAs may be 400mA × 1s or 80mA × 5s, for example, in the case of 400; wherein, 1s is the exposure time, namely the time of applying the tube voltage; mAs represents the total radiation dose, which is the product of the number of emitted electron currents and time. Referring to fig. 3, in an initial state, the controller uniformly distributes the electron emission dose to each group of emission units 1. However, referring to fig. 4, when the amount of electrons received by the feedback module is less than the total electron emission dose obtained by the judgment module, referring to fig. 5, the controller specifically adjusts the number of emission currents according to the operating state of each group of emission units 1.

The above-mentioned embodiments are merely preferred embodiments for fully illustrating the present invention, and the scope of the present invention is not limited thereto. Equivalent substitutes or changes made by the technical personnel in the technical field on the basis of the utility model are all within the protection scope of the utility model. The protection scope of the present invention is subject to the claims.

Claims

1. An X-ray tube, comprising:

the cathode comprises at least four groups of independently arranged emission units, a plurality of independently controlled emission bodies are arranged in any one emission unit, and the emission units are at least distributed in two planes; the emitters in any one emission unit are arranged in a staggered mode; a plurality of baffles are arranged in any one of the emission units so as to separate the emission units into a plurality of independent compartments; the emitters are correspondingly arranged in the compartment so as to reduce mutual interference among the emitters;

the anode is matched with the cathode and comprises a plurality of target bodies matched with the emitter, and the target bodies and the emitter are arranged correspondingly; the target body receives electron-generated X-ray beams emitted from the emitter to perform convergent imaging;

a vacuum space, the cathode and the anode both being located within the vacuum space.

2. The X-ray tube according to claim 1, wherein the X-ray tube further comprises a master control module, the master control module comprises a controller, an amplification module and a plurality of emitters arranged in parallel; the controller is used for improving the base value current signal, and the amplifying module is used for amplifying the electric signal and transmitting the electric signal to the emitter.

3. The X-ray tube of claim 1, wherein a total emitter tube current of all of the emitters is 200mA-800 mA.

4. A CT scanner comprising an X-ray tube according to any of claims 1-3.