TW201350162A - A mobile X-ray unit - Google Patents

Abstract

The invention relates to a mobile X-ray unit(10) comprising a base (2) for accommodating a control unit, a power supply and a cooler and further comprising an articulated displaceable arm (4a) supporting an X-ray applicator (4) comprising an X-ray tube having a longitudinal axis, said X-ray applicator being connected to the base, the X-ray tube comprising an anode for generating an acceleration field and a target for generating an X-ray beam, the anode being disposed substantially parallel to the longitudinal axis of the X-ray tube. The invention further relates to a method of manufacturing a mobile X-ray tube and a method of delivering an X-ray beam.

Description

Mobile X-ray unit

The invention relates to a mobile X-ray unit comprising a base for accommodating a control unit, a power supply and a cooler, and further comprising a hinged displaceable arm for supporting an X-ray device, The X-ray applicator is coupled to the base and includes an X-ray tube having a longitudinal axis and including an anode for generating an acceleration field and an impact target for generating an X-ray beam.

More particularly, the invention relates to a method of making an X-ray unit and a method of providing an X-ray beam.

The incidence of skin cancer has increased in the past 10 years in the 20th century, and professional medical personnel need to invest a lot of spirit in early diagnosis, logistics and providing appropriate treatment. However, it is gratifying that more than 1.3 million new skin cancers are diagnosed each year and increase at a rate of about 5% per year. Increasing exposure to the sun and reduction of the ozone layer without skin protection is the main reason - it is estimated that more than 1 billion euros will be spent each year on the medical costs of the disease. More than 80% of skin cancers occur in the head and neck areas, and 50% occur in patients over 60 years of age. Compared to current demographics, it is expected that by 2025 the elderly population will be twice as large as today.

Non proliferated cancer, which is essentially superficial lesions, can be treated in different ways. First, surgery can be considered. However, the disadvantage is that the waiting time is long and the postoperative treatment is complicated, and the risk of infection may be high after the postoperative trauma. Second, soft X-ray electron irradiation can be considered. This method has the advantage of non-invasiveness, and each treatment course can be as short as 2 to 4 minutes. It is gratifying that the radiation therapy technology is usually used as a finishing treatment to include a certain number of treatments.

Therefore, the more the incidence of skin cancer and the increase in the proportion of the elderly population in the overall demographics, pose a substantial challenge to cancer treatment and treatment materials.

In recent years, it has been generally recommended to use a portable X-ray unit that can be used in the radiotherapy department of a hospital. An implementation of such a portable unit is described, for example, in Patent Publication No. US2007/0076851. As used herein, "mobile" and "portable" are interchangeable and are equivalent to a device that can be easily moved or transported, for example, by a single individual or Transport device.

The above-mentioned unit includes an X-ray source provided with a filtering device having a plurality of filters rotatably correspondingly disposed with a focal point relative to an X-ray tube for changing the filtering characteristics in response to demand. A plurality of filters are disposed in the filter device and are disposed laterally relative to one of the longitudinal axes of the X-ray tube.

A disadvantage of the known X-ray tube is that the beam characteristics may be affected due to the known internal structure of the X-ray tube. For example, it may result in a wider penumbra for the X-ray beam. Another known X-ray tube has the disadvantage that the overall diameter of the X-ray tube is relatively large. More specifically, Known X-ray tubes are known to have the disadvantage of large size and irregular shape due to the presence of a filter carousel. The irregular shape will shift the center of gravity of the known X-ray tube to be eccentric, which will make it difficult to stabilize the known X-ray tube in the treatment position.

It is an object of the present invention to provide a mobile X-ray unit with improved operational characteristics. More particularly, it is an object of the present invention to provide a mobile X-ray unit having an improved X-ray beam penumbra and/or a reduced skin dose when the dose is provided at a depth of 5 mm. Another aspect of the present invention is to provide an improved X-ray unit in which the X-ray tube can be easily stabilized when it is in the treatment position.

Based on this, in a mobile X-ray unit according to the invention, the longitudinal axis of the anode is arranged substantially parallel to the longitudinal axis of the X-ray tube.

It is conceivable that the anode is typically embodied as a body having a true or substantially cylindrical shape.

In accordance with an embodiment of the present invention, a X-ray applicator includes a longitudinal axis, the longitudinal axis of the X-ray tube being substantially parallel to the longitudinal axis of the X-ray device.

In accordance with another embodiment of the present invention, the mobile X-ray unit has a longitudinal axis of the anode, a longitudinal axis of the X-ray tube, and a longitudinal axis of the X-ray treatment device that are co-axially disposed.

It can be found that by coaxially aligning the anode relative to the substantially cylindrical outer Type X-ray tube and X-ray device, the resulting X-ray beam can extend along the longitudinal axis of the X-ray device, whereby the collimator is appropriately opposed to X. When the beam of light is aligned, a narrower penumbra can be achieved. In addition, the coaxial structure will simplify the installation of the X-ray tube member and reduce the overall weight of the X-ray treatment device.

In addition, for skin illumination applications, it may be desirable for the X-ray applicator to be in a vertical orientation or with only a small tilt relative to the vertical axis. Accordingly, by placing the body of the anode parallel to the longitudinal axis of the X-ray device, the mechanical balance of the device during use will be improved.

According to another embodiment of the mobile X-ray unit of the present invention, the anode includes an exit window for emitting X-rays generated by the impact target, and the X-ray tube further includes a collimator for molding. The X-ray beam, the impact target, the exit window, and the collimator are disposed substantially at intervals along the longitudinal axis of the X-ray tube.

More preferably, the impact target, the collimator and the exit window are usually mounted in different positions in the X-ray tube. More preferably, the impact target is provided on an outer surface of the anode, and The upper axis is perpendicular to the longitudinal axis of the anode.

It can be seen that, in the case where the impact target, the collimator and the exit window are disposed at intervals on the longitudinal axis of the X-ray tube, preferably, the X-ray tube is allowed to have a substantially coaxial geometry. The center of gravity of the X-ray tube assembly can be located at or near the longitudinal axis of the X-ray tube, whereby the X-ray tube can be easily positioned in space without the biasing force being applied to its center of gravity. More preferably, the X-ray tube has a rotational symmetry to Less has a substantial weight relative to the component.

It can be further found that when the X-ray tube is provided with an end exit window on the longitudinal axis of the X-ray tube, and the extension of the X-ray beam is substantially parallel to the longitudinal axis of the X-ray tube, the beam of the X-ray tube Features can be improved. In particular, it is possible for the X-ray beam to have a narrower penumbra than conventional techniques.

Further, in accordance with the configuration of the X-ray tube in the X-ray unit of the present invention, it is advantageous from a mechanical point of view that the balance of the X-ray tube on the articulated arm is simplified by the coaxial geometry. More preferably, for an X-ray tube, it is housed in an outer casing that is relatively slim (outer diameter less than 10 cm) and elongated (approximately 30 cm in length). More preferably, it is located in the vertical direction providing the X-ray beam to the patient. Once the internal geometry of the X-ray tube is coaxial, the center of gravity is located on or near the longitudinal axis of the X-ray tube, so that the weight of the X-ray tube can be properly balanced, and the hinged arm can be easily and repeatedly displaced. Supports the X-ray device. Similarly, positioning the X-ray tube at a slight angle is simplified because relatively small deflection forces are applied to its center of gravity relative to conventional techniques.

According to an X-ray unit according to an embodiment of the present invention, the distance between the impact target and the collimator is about 4 to 10 cm, and the better distance is about 5 to 6 cm.

It can be found that the distance between the X-ray impact target and the collimator is set to be about 4 to 10 cm, and the better distance is about 5 to 6 cm, which can improve the beam characteristics. For example, it can be found that, surprisingly, when the distance between the impact target-collimator is 4 to 10 cm, it is better that the distance is about 5 to 6 cm because of its relatively small focus size. Improving the flatness of the beam and the narrower penumbra can be achieved. For example, when hitting a target-collimator When the distance between them is about 5 cm, a penumbra of 1.5 to 1.8 mm can be achieved (specifically 20/80% of the line). More preferably, the total length of the X-ray device can be between 10 and 30 cm, and the X-ray device can be adapted to be illuminated by the device in contact with or near the skin. From a geometric point of view, the configuration of the present invention has a relatively small distance from the impact target to the collimator and the exit window, thereby reducing the amount of scattering radiation and thus the penumbra relative to conventional systems. The area is narrower. Such a narrow penumbra is very important for the treatment of smaller lesions, such as skin cancer, which is minimized for healthy tissue doses, which is a key item for dose dosing solutions. More preferably, the distance between the collimator and the exit window can be minimized.

In accordance with another embodiment of the present invention, the collimator can be provided with an automatic identification device configured to generate a signal representative of the characteristics of the collimator in the control unit.

This advantage can be found in that it fully automatically recognizes that the collimator is inserted into the X-ray tube, and that human error for defining the range geometry can be minimized or even eliminated. For example, when the collimator is housed in a chamber, the chamber can be provided with a resistive path whose resistance value can be changed. The collimator can then be provided with a projection adapted to cooperate with the resistance path of the chamber, thereby changing the final resistance and thus generating a representative signal of the inserted collimator. Even better, this signal can be provided independently as a control unit for the mobile X-ray unit. More preferably, the X-ray unit includes a set of collimators having respective identification devices.

According to another embodiment of the present invention, a portion of the X-ray unit may include a plurality of contact pins adapted to be coupled to the collimator. Each of the different types of collimators can be provided with at least one contact pin at a uniquely defined position such that when one of the contact pins is contacted in the X-ray unit, it provides or completes an electrical circuit. Each contact combination occurs on a different type of collimator at different locations of the collimator, thus providing a unique identification of each type of collimator. When the collimator is connected to the X-ray unit, it completes a specific circuit, and the control unit will detect the completion of the different circuits and send a signal to the control unit to identify which type of collimator is placed.

Alternatively, the automatic collimation identification device may comprise magnetic, optical, radio frequency identification (RFID) or other configuration, for example, a suitable bar code may be provided on the collimator, which may be read out prior to the device ready state. To confirm.

According to another embodiment of the present invention, an X-ray unit can be provided with a signal device for indicating the generation of an X-ray beam.

The benefit of providing this signal device is that it can be discerned that the X-ray beam is on. For example, this signal can be located on an X-ray device with a suitable light source. One or more light emitting diodes can be used based on this. A plurality of signal devices can also be provided corresponding to the energy of the generated X-ray beam.

For example, for the lower portion of the X-ray beam spectrum (about 50 KV), a first indicator, such as a first color light, can be used; for the middle portion of the spectrum (about 60~) 65KV), a second indicator can be used, such as a second color light; finally, for the higher part of the spectrum (about 66~75KV, more preferably 66~70KV), a third indicator can be used, such as The third color of light. It will be understood that there may be a plurality of possibilities for indicating different spectra, including but not limited to the hard X-ray beam provided. Hardening with progressive illumination of a plurality of indicators. It will also be appreciated that the indication of the KV range is permissible in the device, in a user interface, or in an implementation unit. More preferably, the above KV ranges are scaled, such as 1,1; 1, 2; 1, 3; 1, 4; 1, 5.

An X-ray unit according to another embodiment of the present invention, wherein the cooler is provided with a conduit for providing a cooling medium adjacent to the X-ray tube, the wiring of the conduit being located in the X-ray tube and associated with the X-ray tube Between the walls of a housing.

It has been found that the advantage of providing a space between the outer surface of the X-ray tube and the inner surface of the housing other than the X-ray device is that the space can be at least partially filled with refrigerant. The benefit of using recycled water as a cooling medium is its specific heat capacity, which provides improved heat transfer relative to the gas. However, compressed gas can also be used as a suitable refrigerant. More preferably, the temperature sensor is disposed on the outer casing of the X-ray device to measure the actual temperature of the outer casing. This temperature sensor can be connected to a control unit for controlling the cooler and/or for controlling the high pressure supply. When the temperature rises to a predetermined shutdown value, the control unit can control to shut down the high pressure supply and/or increase the cooling mode, for example, by increasing the pumping capacity of the refrigerant.

In an X-ray unit according to another embodiment of the present invention, a radiation detector can be provided in the outer casing for detecting an X-ray beam.

It can be found that it is advantageous to provide a separate device for detecting the presence or absence of the generated X-ray beam. More preferably, the X-ray unit according to the present invention includes a primary timer which is set for a time for high The pressure supply is provided to provide a predetermined radiation dose. The radiation sensor housed in the housing outside the X-ray device can be part of a second timer, the loop of which is adapted to close the high voltage supply when the predetermined radiation dose is reached. In this way, radiation safety control can be improved.

In accordance with another embodiment of the present invention, an X-ray unit includes an exit surface that is intended to be oriented toward a patient, the outlet surface being covered by a tamper cover.

It can be found that the benefit of providing such a therapeutic cover is that it can have multiple functions when in use. First, the applicator cover can be used to protect the X-ray exit surface of the X-ray device from contamination during the clinic. Secondly, the thickness of the applicator cover in the direction of extension of the x-ray beam can be selected to be sufficient to substantially eliminate electron contamination from the x-ray beam. It is known from the prior art that the energy of the secondary electrons emitted from the X-ray tube and the thickness required for the use of the material, such as plastic, glass, ceramics, etc., are sufficient to completely intercept such electrons. More preferably, the cap is attached to the disposable device. In general, the thickness of the cap of the applicator can be in the range of about 0.3 to 3 cm for a useful X-ray beam.

Third, the cap can be used as a heat absorber to reduce the temperature of the X-ray device, and based on this, the patient only feels that the device has only a slight warmth when it comes into contact with the skin.

According to another embodiment of the present invention, the X-ray unit is connected to the base by a displaceable panel, and the elastic line is substantially wired in the displaceable panel.

It can be found that an intermediate mechanism unit is provided to connect the mobile X-ray single The base of the element and the X-ray device are advantageous in order to encapsulate the elastic line and thereby prevent the entanglement of the line. The displaceable panel can be configured to have a predetermined travel distance relative to the lowest position and the highest position. This predetermined moving distance is advantageous for increasing the durability of cable lines and lines of the X-ray unit, particularly the piping containing the refrigerant.

According to another embodiment of the present invention, the X-ray unit includes a user interface for controlling the X-ray unit. More preferably, the user interface includes a display. For example, the display can be implemented as a touch screen configured to input data. Alternatively, the display can be configured to echo data, and any dedicated button or other suitable device can be provided to the X-ray unit for inputting data.

According to another embodiment of the present invention, a method for manufacturing a mobile X-ray unit includes a base for accommodating a control unit, a power supply and a cooler, and further comprising an articulated displaceable arm Supporting an X-ray device comprising an X-ray tube, the X-ray tube having a longitudinal axis and including an anode for generating an acceleration field, and an impact target for generating an X-ray beam, The method according to the invention comprises the following steps: The X-ray applicator is coupled to the pedestal using a connector that includes a resilient line; the X-ray tube is configured such that the longitudinal axis of the anode is disposed substantially parallel to the longitudinal axis of the X-ray tube.

More preferably, the anode includes a strike target for generating an X-ray beam, and the X-ray tube includes an exit window and a collimator for shaping the X-ray beam generated by the impact target. Among them, the steps include configuring the impact target and the exit. The window and the collimator are arranged substantially at intervals on the longitudinal axis of the X-ray tube.

In a particular embodiment, the impact target, the collimator, and the exit window can be disposed generally parallel to each other and generally at right angles to the longitudinal axis of the X-ray tube.

More preferably, in accordance with an embodiment of the present invention, the X-ray unit, the impact target and the collimator are housed in a substantially cylindrical X-ray device, wherein the X-ray beam is extended. It is roughly parallel to the longitudinal axis of the X-ray device. More preferably, embodiments of the method according to the invention will be described later with reference to FIG.

According to the present invention, a method of providing an X-ray beam to illuminate a lesion surface by using an X-ray unit, wherein the X-ray unit includes a base for accommodating a control unit, a power supply and a cooler, and The utility model comprises an articulated displaceable X-ray arm for supporting an X-ray device, the X-ray device is connected to the base and comprises an X-ray tube, the X-ray tube has a longitudinal axis and comprises an anode for generating a The acceleration field and a strike target are used to generate an X-ray beam, the longitudinal axis of the anode being disposed substantially parallel to the longitudinal axis of the X-ray tube.

More preferably, for the X-ray unit, the mobile X-ray unit as described above is used.

The invention further relates to a medicated device cover for an X-ray unit, the X-ray unit comprising an X-ray tube housed in an X-ray device, the X-ray device comprising an exit surface predetermined toward a The patient, and the medicated cap is configured to cover at least the exit surface. Even better, the applicator cover is disposable. More preferably, the thickness of the illuminator cover in the direction in which one of the X-ray beams extends is sufficient to substantially eliminate electron contamination from the X-ray beam (electron) Contamination). The applicator cap is advantageously made of a substantially transparent material such that the contour between the exit surface of the X-ray applicator and the lesion to be treated can be pre-conceived. More particularly, the present invention relates to a mobile X-ray unit as described above and is provided with the above described applicator cover.

The above described objects, features, and advantages of the invention will be apparent from the embodiments of the invention. range.

The details disclosed in the specific embodiments of the present invention will be described in detail in conjunction with the drawings.

Figure 1a is a schematic diagram showing a mobile X-ray unit in accordance with an embodiment of the present invention. The mobile X-ray unit 10 includes a base 2 including at least one power supply unit, a cooling system, and a control unit for controlling an X-ray device (X-ray). The operation of the applicator 4 includes an X-ray tube housed in an outer casing. The X-ray device 4 is connected to the base 2 by a flexible cable 3 and can be at least partially housed in a displaceable panel 5. The X-ray applicator 4 is supported by an articulated displaceable arm 4a which may include a pivot for changing the position of the X-ray applicator 4 in space. The X-ray treatment device 4 includes a longitudinal axis 4b and an exit window 4c through which the X-ray beam generated can be emitted. The hinged displaceable arm 4a can also be mechanically coupled to the displaceable panel 5, whereby Change the vertical portion of the X-ray treatment device 4. More preferably, the displaceable panel 5 is provided with a handle 6, whereby it can be easily operated. The displaceable panel 5 can be guided by a suitable rail so as to be substantially smooth and shock-free when displaced. The base 2 can be provided with three or more wheels to move the X-ray unit to different positions. The wheels are mounted by suitable bearings so that the X-ray unit can be moved by a single individual. More preferably, the wheels are interconnected by a deformable frame which ensures that all of the wheels can be in contact with the surface beneath them, such as on the floor or the ground, even when the surface is uneven.

According to one aspect of the invention, the X-ray device is housed in an X-ray tube having a coaxial geometry, wherein the target, the exit window, and the collimator (collimators) are parallel to each other. The exit window, the impact target, and the collimator extend substantially perpendicularly over the longitudinal axis 4b of the X-ray tube. More preferably, the X-ray tube has a rotational symmetry with respect to the impact target, the collimator, the appropriate filter and the exit window. More preferably, the center of gravity of the X-ray tube according to the present invention is disposed on the longitudinal axis 4b.

More preferably, the cradle 2 is provided with a display 7 for feeding-backing the desired user information. The display 7 can be configured with a touch-sensitive screen for inputting appropriate data to the system.

Figure 1b is a schematic diagram showing a displaceable panel of a mobile X-ray unit in accordance with an embodiment of the present invention. In the enlarged schematic form, the component symbol 10a refers to a specific component of the displaceable panel 5. Based on this, the grip 6 It can be used as a mechanical member to pull or push the displaceable panel 5. Alternatively, the grip 6 can be configured as an electronic actuator for triggering the motor (not shown) to displace the displaceable panel 5. For example, when the grip 6 is pulled, the motor can be activated so that the displaceable panel 5 can be displaced in the direction A, and pushing the grip 6 can make the displaceable panel 5 Direction B drops. More preferably, the mobile X-ray unit includes means for limiting the displacement of the displaceable panel 5. This has the advantage of ensuring the mechanical stability (limitation of the upper level) of the system on the one hand and the limitation of the lower level on the other hand. More preferably, the displaceable panel 5 can be moved using a built-in rail, the length of which can be selected to limit the range of movement of the displaceable panel 5 in a desired manner.

The pedestal 2 preferably includes a display 7 that functions as a suitable user interface 7a. For example, patient information such as a photo of the patient and/or a photo of the condition can be displayed in the window ( On the window 7b, the related patient information such as birthday, sex, dose prescription, and dose delivery protocol can be displayed on the window 7c. A button 7d can provide a touch function to input data, or a suitable hardware switch or button can be provided as appropriate.

Fig. 1c is a schematic view showing a displaceable function medical device of an X-ray unit according to an embodiment of the present invention. In accordance with one aspect of the present invention, the mechanism of the mobile X-ray unit is developed and constructed to support the X-ray applicator 4 to have a greater range of movement and rotational displacement.

Reference numeral 11 denotes a schematic embodiment in which the X-ray applicator is located in a parked position. For the sake of clarity, no lines are shown. In this position, it may be adapted to transmit the mobile X-ray unit towards a room and/or to be mobile near the patient. In order to retract the X-ray applicator as close as possible to the base 2, the hinged displaceable arm 4a is bendable under the outer portion 5a of the displaceable panel 5. In order to ensure the stability of the mobile X-ray unit during its maneuvering, a load block 2a close to the floor is provided to reduce the absolute position of the gravity point of the overall structure.

Reference numeral 12 denotes a schematic embodiment in which the X-ray treatment device 4 is located in one of the working positions, having an x-ray exit surface 8 facing the patient P, in order to The X-ray applicator has a suitable position relative to the patient P, and the displaceable panel is movable to a predetermined dwell position between the lowest position and the highest position of the displaceable panel 5. The hinged displaceable arm 4a can be used to properly rotate the X-ray applicator according to a rotational axis. More preferably, the selection of the axis of rotation is the imaginary direction of the X-ray beam emitted from the exit surface when the X-ray tube is in the vertical direction.

Reference numeral 13 denotes an exemplary embodiment in which the X-ray treatment device 4 is located at the lowest position, for which purpose the displaceable panel 5 can be located at its lowest position and the hinged displaceable arm 4a can be oriented to the X-ray in a desired manner. Therapy.

2 is a block diagram showing the structure of a mobile X-ray unit according to an embodiment of the present invention. The mobile X-ray unit according to the invention comprises a high voltage supply, and more preferably, is suitable for a suitable The X-ray tube produces X-rays of 50 to 75 kV, a cooling system for cooling the X-ray tubes in use, and a control system for controlling the sub-units of the X-ray units during use (sub- Unit) electronic and electrical parameters. The component symbol 20 refers to the main unit of the control system 21 and the X-ray applicator 22.

The control unit 21 preferably includes a hard wired user interface 21a for switching the opening and closing of the high voltage supply 21b. More preferably, the high voltage supply 21b includes a high voltage generator 21c having improved ramp-up and ramp-down characteristics. More preferably, the ramp-up time is approximately 100 ms. The hardwired user interface 21a can be configured to automatically activate a cooling system 21d when the high voltage generator is turned on. Additionally, control unit 21 can include a primary controller 21e configured to control dose delivery when the X-ray device is in use. The primary controller 21e can provide a primary counter to delete the logged-in data after the X-ray illumination is initialized. This master calculator automatically shuts down the high pressure supply to the X-ray tube after reaching the established dose. The high voltage supply can be configured to provide 200W of power when in use. More preferably, the established dose is at least dependent on the energy and dose rate at which X-rays are produced. Wherein, the above situation can be calibrated in advance, and corresponding calibration data is provided as much as possible, so that the main dose distribution control of the main controller can be achieved. More preferably, the secondary controller 21f is provided to initiate the dose. The dispensing control is an independent circuit, and the secondary controller 21f can be connected to a dose meter that is housed in the X-ray device, in the X-ray range before the collimator. Accordingly, the dose meter can be assigned to the actual dose, providing immediate data in view of changes in the dose during ramp up and ramp down of the high pressure source. Also preferably, the control system may further include a safety controller 21g adapted to read data from the primary controller 21e, and the secondary controller 21f to close the high voltage generator after the desired dose is dispensed. (high voltage generator) 21c. Alternatively, or in addition, the safety controller 21g can be coupled to an emergency stop, a door interlock, and a generator interlock.

The X-ray applicator 22 preferably includes the following features: an X-ray tube 22a pre-packaged in an outer housing 22k. In accordance with the present invention, the X-ray tube has mutually colliding targets, collimators, and exit window structures such that the resulting X-ray beam extends substantially parallel to the longitudinal axis of the X-ray tube. More preferably, the X-ray tube has a distance of about 4 to 10 cm, more preferably about 5 to 6 cm, between the target-collimator. The X-ray treatment device may further include a beam hardening filter 22b selected to intercept low-energy radiation and a beam flattening filter 22c to intercept portions The X-ray radiation is used to produce a substantially flat beam profile near the exit surface of the X-ray applicator. Still further, the X-ray applicator 22 can include one or more collimator configurations to define the processing beam geometry. better one Yes, a set of collimators can be used, for example, having diameters of 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5 cm. More preferably, although a circular collimator is considered here, any form of collimator such as square, elliptic or custom made collimator Can be used. It can be found that the X-ray treatment device 22 provided with the automatic collimator detection mean 22f has the advantage that it is suitable for automatically signaling the collimator in use. More preferably, resistance sensing is used wherein each collimator is provided with at least one pair of projections for bridging the resistive path provided in the collimator receptacle. The resistance generated by this chamber constitutes the signal representative of the collimator in use. The X-ray applicator 22 preferably includes a built-in temperature sensor adapted to emit temperature signals from the X-ray tube and/or its housing. The signal from the temperature sensor is received by the control system and loaded with an analysis system. Once the measured temperature rises beyond the allowable range, an alarm signal is generated, optionally, a high voltage is also provided. The shutdown signal of the generator. The X-ray device 22 further includes a radiation sensor 22h disposed inside the outer casing 22k for detecting the actual X-ray radiation emitted by the X-ray tube. More preferably, based on safety factors, the X-ray charge device 22 can further include a non-volatile data storage 22i for recording at least the operational parameters of the X-ray tube. Further, in order to enhance the safety of the radiation, the X-ray treatment device 22 can provide a radiation indicator 22j to provide a visual and/or an audio output for the user and/or patient to know X. The on/off state of the light pipe. Better Yes, the radiation indicator 22j may include a plurality of distributed signaling means, and more preferably, at least one signal device, for example, a light-emitting diode (LED) electrically connected to the X-ray treatment Device 22. More preferably, the signal device is provided on the X-ray device 22.

3 is a cross-sectional view showing an X-ray applicator of a mobile X-ray unit according to an embodiment of the present invention, and an X-ray applicator 30 includes an outer housing 36. There is an X-ray tube assembly 35 having an external shielding 35a. The X-ray applicator 30 further includes an anode 45 having a strike target 45' on its outer surface and configured to emit a beam of X-rays having a longitudinal propagation axis 45a, and The longitudinal axis of the X-ray tube is matched. In accordance with the present invention, the anode 45 is configured such that its longitudinal axis is substantially parallel to the longitudinal axis of the X-ray tube such that the X-ray beam extends substantially along the longitudinal axis of the X-ray tube assembly 35. More preferably, the impact target portion, the exit window and the collimator of the anode of the X-ray tube are parallel to each other and are arranged substantially vertically on the longitudinal axis 45a and spaced apart from each other. It has been found that in order to configure the exit window located on one end surface of the X-ray applicator 30 as a balanced mechanical structure of the X-ray applicator 30, it is conceivable that the center of gravity of the structure can be set to X. This is achieved by the longitudinal axis 45a of the light pipe assembly 35.

More preferably, the distance between the impact target (anode) and the collimator 33 is about 4 to 10 cm, more preferably about 5 to 6 cm, so that the relatively short impact target-collimation An instrument distance of about 5 cm is advantageous for generating an X-ray beam with a substantially narrow penumbra (per 20/80% line) Approximately 1.5-1.8 mm) and better beam flatness. The above distance between the anodes is as long as the distance between the impact target 45' and the midplane of the collimator 130.

The X-ray applicator 30 further includes a filter 39 to harden the X-ray beam emitted from the impact target 45', a beam flattening filter 40 to flatten the beam profile, and a collimator 33, inserted in a collimator receptacle 41.

In order to avoid overheating of the X-ray tube during use, a cooling system 34 will be provided, advantageously disposed between the X-ray tube assembly 35 and the external mask 35a, and with the X-ray tube assembly 35. The surfaces are in contact. A suitable refrigerant can be provided by a pipe 31. More preferably, the refrigerant is recyclable and can be water, a suitable oil body or even a compressed gas. The X-ray device may further include a temperature sensor 37.

The X-ray applicator 30 can further include a suitable radiation detector 38 coupled to a radiation indicator 43. More preferably, the data collected by the radiation detector 38 is stored to a data storage unit 44.

To protect the X-ray exit surface of the X-ray applicator 30 from contamination across the patient, an applicator cap 42 may be provided to cover at least the exit surface of the X-ray applicator 30. More preferably, the thickness of the applicator cover is thick enough to completely intercept the secondary electrons emitted by the X-ray device.

Figure 4 is a view showing an X-ray treatment device according to an embodiment of the present invention. Figure 3 is a schematic view of the applicator cap. More preferably, the cap is made of polyvinylidene fluoride (PVDF) and has a thickness of about 0.4 to 0.7 mm across the window portion. More preferably, it is 0.6 mm and has a density of about 1.75 to 1.8, more preferably 1.78. Alternatively, the cap is made of polyphenylsulfone (PPSU) and has a thickness of about 0.3 to 0.6 mm, more preferably 0.5 mm, and about 1.30 to 1.45. The density is better for a density of 1.39. It has been found that the above materials are particularly suitable for use herein due to their stability under the influence of X-rays and are suitable for different types of sterilization, such as chemical sterilization or sterilization at elevated temperatures.

The applicator cover 42 is preferably permeable to X-rays and can be made of glass, clear plastic or ceramic. The caps may also be made of metal, although this is not optimal. In the last case, the applicator cover 42 can be sterilized. However, it is even better to use a disposable heat treatment device cover. In the fourth drawing, the component symbol 50 indicates that the outer diameter of the X-ray applicator 51 is larger than the outer diameter of the outlet portion, and is covered by the heat treatment cover 42. Although this embodiment can reduce the total weight of the X-ray applicator, the outlet portion can be the same diameter as the body of the X-ray applicator 51.

Figure 5 is a schematic diagram showing a collimator having identification means in accordance with an embodiment of the present invention, the collimator 63 having a central opening 64 to define as shown in Figure 3 The shape and size of the X-ray beam emitted by the X-ray device 30. The collimator 63 is adapted to be housed in a collimator receptacle 61 that can be shaped as a suitable chamber such that the collimator 63 can be stably fixed. In order to be able to have an identification of the automatic collimator 63, the collimator is provided with two projections 65a, 65b adapted to cooperate with a resistive path 62 provided in the collimator chamber 61, When the projections 65a, 65b are in contact with the resistive path 62, the net resistance of the collimator chamber will vary. The change in resistance of the collimator chamber can be used as an automatic identifier for the collimator to be inserted into the collimator chamber. More preferably, for a set of collimators, each collimator needs to have a unique pair of protrusions to distinguish the change in the net resistance of the collimator chamber. It is known from the known art that the plurality of pairs of projections 65a, 65b can have different relative positions on a surface of the collimator.

Fig. 6 is a view showing a collimator having an identification device according to another embodiment of the present invention, and an embodiment of the collimator 33 different from that shown in Fig. 3 will be described in detail below. The collimator 33 can be provided with an aperture 71, which can have any shape, and identification means 72a, 72b can be used to automatically detect whether the correct (required) collimator is inserted into the X-ray treatment. In the device. For example, the identification device 72a, 72b may be a suitable spring loaded pin to cooperate with the resistor body (as indicated by the symbol 33a) to change the net resistance of the resistor body by detecting the absolute body of the resistor body. Or the representative signal of the relative resistance, the automatic identification of the inserted collimator can be realized.

The symbol of the component symbol 33a is a schematic diagram showing the implementation of the resistor body, wherein each dashed line 74a, 74b, 74c, 74d, 74e, 74f represents each resistor contact ring (only a few are drawn for clarity), the resistance path The net resistance change of 33a depends on which pin of the net resistor is in contact with the pin 72a or 72b. It depends on the contact and changes depending on where it is touched. Different types of collimators 33 can be coded depending on the different locations of the contact pins 72a, 72b of the outer surface 70.

In another embodiment of the collimators 33', 33", the contact pins 72a, 72b can assist with a contact bar 76 for locking and/or enabling the collimator to be properly inserted into a quasi-aligner In the straight chamber, this feature is particularly advantageous when the collimator does not have a symmetrical geometric shape.

In another embodiment, the collimator and/or pin may be color coded.

In another embodiment, as shown in Fig. 6, a collimator 70 is provided. The collimator defines a hole 71 through which the X-ray can pass. The collimator is provided with a pair of contact pins 72a, 72b. When mounted on the X-ray device 30, the pin will be in mating engagement with a receiving pad on the mating connection of the X-ray device 30. The receiving device can be formed with a flat region having a plurality of contact pads 74a-74f arranged around the lower base portion of the X-ray applicator 30. Thus, when the collimator is located in the collimator housing chamber and is in a stable position, a pair of contact pads will be coupled to the contact pins of the X-ray applicator 30. Each different size collimator will have a unique contact pin arrangement to contact a particular pin of one of the X-ray applicators 30. Each pin can be coupled to the control unit of the base 2 such that a particular and distinct circuit can be used to distinguish the collimator and a particular identification signal can be transmitted to the display 7. This method facilitates contact only between the pad and the contact pin and does not require the implementation of a measuring resistance (conducting) value. This is advantageous because it minimizes contact with soiling or contamination, this one is slightly Minor errors can affect the data being read, which in turn leads to erroneous treatment procedures. Various configurations of contact pins and pads are possible. In this way, collimators of different specifications can be clearly identified.

Alternatively, it may be provided that each collimator has an electronic identification device, for example, a wafer having a plug, when the pin is inserted into the collimator chamber (provided with a corresponding socket), collimation The instrument identification device will be in electrical communication with the control unit of the mobile X-ray unit.

Figure 7 is a schematic view showing an X-ray tube according to another embodiment of the present invention, and Figure 7E-E is a cross-sectional view taken along line EE in Figure 7, and Figure 7F-F is shown in Figure 7 A cross-sectional view of the section line FF. The X-ray tube 100 has a body 102, one end is a closed end, and the other end is an end window 104, and X-rays are emitted therefrom. The end window is made of thin sheet of Beryllium. Other metals that are suitable for X-rays are also feasible. The end window 104 is covered by an applicator cap 106 to protect the window portion from damage and to protect against metal toxic effects. The applicator cover 106 is preferably made of a plastic material.

In the tube body 102, a strike target 108 is located about 4 to 10 centimeters from the collimator 130, and more preferably about 4 to 6 centimeters from the collimator 130 (see section 7F). -F map). The impact target 108 is fabricated from Tungsten metal to provide the desired X-ray spectrum. The tungsten tip of the impact target 108 is mounted on a large anode assembly 110, which is also provided as a function in the impact target 108 to conduct heat generated by the generation of X-rays. Most anodes The assembly is made of copper. The cathode 112 is located slightly off-axis near the end window, and the electrons emitted from the cathode are accelerated across the potential difference between the cathode and the anode, which is set to about 70 KV in this example, and reaches the impact target as in the prior art. 108, where the X-ray is struck and X-rays are generated, and the X-rays emitted from the impacting target 108 are subjected to a beam hardening before passing through the collimator 130 and passing through an exit surface 124 on the medicated cap 106. Beam hardening filter 122. The collimator 130 can be mounted on a suitable collimator receptacle 128.

The anode assembly 110 is mounted in the body 102 and is electrically insulated. Several known techniques and conventional materials can be used to provide the desired degree of insulation between the anode and the body 102.

As is known in the art, the generation of X-rays generates a large amount of waste heat, and therefore, it is necessary to maintain the tube cooling below a safe temperature. A variety of cooling mechanisms are known and can be used. In the present embodiment, the X-ray tube is cooled by means of forced cooling around the anode region with cooling water, the cooling water entering the back of the tube by conduit 116, and by a second conduit 118 And leave. The water cooling circuit is a closed loop circuit with a remote cooler (not shown) before the water leaves the tube to be cooled and before the return tube. Alternatively, oil or other fluids may be used as a cooling medium. In some applications, compressed gas can also be used as an effective coolant.

As in the prior art, X-rays are generated and emitted in all directions, except for the shelter of the tube body 102 and other internal component shields, thereby minimizing the amount of radiation from the tube body and making more radiation. Shot from the end window Out. The thickness of the mask provided by the tube is designed to at least provide the minimum level of shading required for safe use by the user.

A high voltage cable assembly 120 is coupled to the anode assembly 110. The high voltage line assembly is connected to a flexible cable means (not shown) which is in turn connected to the high voltage power supply.

A radiation detector 114, see Fig. 7E-E, is disposed outside the path of the X-ray beam exiting the impact target 108 to the end window 104. The detector can be any known amplitude. Shoot the detector. In this embodiment, it is connected to an amplifier using a conventional radiation hardened semi-conductor. When the X-ray tube 100 is operating and emits X-ray energy, the radiation detector 114 begins to detect. The output of the detector is coupled to a control unit whereby the output signal can be used to provide an optical indication to the user to confirm that the X-ray tube is in operation. The device can provide an X-ray detector for detecting whether the X-ray tube is activated or deactivated.

More preferably, through the radiation detector 114, the determination of the arrival of the patient and the calculation of the X-ray dose can be controlled during the course of treatment. This device can have an instant dose control system whereby the precise dose of radiation can be determined. Once the dose rate can be determined, the treatment schedule can be adjusted. This has the advantage of achieving an accurate and precise X-ray dose control that is to be controlled.

In order for the tube body 102 to be properly placed on a tumor, a tumor illumination device is used. The tumor illumination device can include a plurality of A light 126 is placed at the periphery of the tube near the end window. When used, the light from the source is on the patient's skin. Since the light source 126 is located around the circumference of the tube body 102, a small distance from the end of the tube, a circle of light is created, the interior of which is empty. In this way, the position of the light creates a shadow at the tube body 102. This shaded circle is used to indicate the area where the target is radiated when the X-ray tube is activated. The inside of the circle will not be completely black, as ambient light will enter this shaded area.

More preferably, the light source 126 is a white LED that is bright enough to clearly illuminate the target area without excessive heat generation and a long lifetime. It is important to have no heat generated because the source is very close to the patient's skin and, as importantly, the risk of skin burns or other damage can be minimized. Light-emitting diodes of other colors can of course also be used. Alternatively, other sources of light may be used, such as a conventional filament lamp, or even a remote light connected to a ring by a fibre optic cable.

Figure 8 is a schematic view showing an X-ray tube according to another embodiment of the present invention. According to the present invention, an indicator 126 is provided on one side surface of the X-ray tube assembly 35, and the indicator 126 may include a Light-emitting diodes or other suitable light source. The light generated from the indicator 126 is affected by the reflective surface of one of the X-ray collimators 132, after which the light is further reflected by the reflective surface 134, thereby becoming the independent beams B1 and B2, towards the central axis of the X-ray tube. (central axis) X.

Advantageously, the X-ray tube assembly 35 is suitable for forming and manufacturing to provide a counter A reflective body 134, which may be a concentric reflective ring connected to a corresponding recess of the X-ray tube.

More advantageously, the reflective surface 134 can advantageously be provided on a collimating instrument surface facing away from the patient toward the X-ray source (not shown) and disposed on the axis X. Thus, the prior art knows how to configure the collimator and the X-ray tube, as shown in Fig. 3, so that the structure as discussed in Fig. 6 is feasible. One of the light spots produced by indicator 126 as previously described can be used to accurately position X-ray tube 35 relative to patient P.

More advantageously, the spatial position of the intersection between the beams B1 and B2 can be selected to provide a spot on the X-ray device from the receiving X-ray tube 35 (Fig. One of the outer surfaces is not shown to fit one of the established distances. For example, the predetermined distance can be chosen to be 1, 2, 3, 4, 5 centimeters from the surface of the X-ray device. In this way, accurate alignment between the desired treatment area on the patient P and the central axis of the X-ray beam can be controlled and maintained. More preferably, the predetermined distance can be selected from the outer surface of the X-ray device to be about 2 to 3 cm so that the X-ray device has a maneuvering line without the risk of contact with the patient. When the X-ray applicator is placed relative to the patient P, it is possible to further utilize suitable precision mechanical positioning using the articulated arm 4a and the indicator as shown in Fig. 1a.

More advantageously, when the indicator and the reflective body are referenced to the X-ray tube 35, it is possible to achieve a smaller configuration of the connection indicator 126 to one of the outer surfaces of the tamper 4 as shown in FIG. In this case, special reflections can be used Instead of using a collimator to achieve reflection.

The present invention has been described above with reference to the preferred embodiments thereof, and is not intended to limit the scope of the present invention, and the invention may be modified and modified without departing from the spirit and scope of the invention. The scope of the invention is defined by the scope of the appended claims.

2‧‧‧Base

3‧‧‧flexible cable

4‧‧‧X-ray applicator

4a‧‧‧ articulated arm (articulated displaceable arm)

4b‧‧‧Longitudinal axis

4c‧‧‧Exit window

5‧‧‧Displaceable panel

5a‧‧‧outer portion

6‧‧‧Handle

7‧‧‧Display

7a‧‧‧user interface

7b‧‧‧window

7c‧‧‧window

7d‧‧‧ button (button)

8‧‧‧X-ray exit surface

10‧‧‧mobile X-ray unit

21‧‧‧control unit

21a‧‧‧user interface

21b‧‧‧high voltage supply

21c‧‧‧high voltage generator

21d‧‧‧Cooling system

21e‧‧‧primary controller

21f‧‧‧secondary controller

21g‧‧‧safety controller

22‧‧‧X-ray applicator

22a‧‧‧X-ray tube

22b‧‧·beam hardening filter

22c‧‧·beam flattening filter

22d‧‧‧collimator

22e‧‧‧applicator cap

22f‧‧‧Automatic collimator detection mean

22g‧‧‧ housing temperature sensor

22h‧‧‧radiation sensor

22i‧‧‧non-volatile data storage

22j‧‧‧radiation indicator

22k‧‧‧outer housing

30‧‧‧X-ray applicator

31‧‧‧pipe

33, 33', 33" ‧ ‧ collimator

34‧‧‧Cooling system

35‧‧‧X-ray tube assembly

35a‧‧‧External shielding

36‧‧‧outer housing

37‧‧‧temperature sensor

38‧‧‧radiation detector

39‧‧‧Filter

40‧‧‧beam flattening filter

41‧‧‧collimator receptacle

42‧‧‧Applicator cap

43‧‧‧radiation indicator

44‧‧‧data storage unit

45‧‧‧Anode

45'‧‧‧ impact target (target)

45a‧‧‧longitudinal propagation axis

51‧‧‧X-ray applicator

61‧‧‧collimator receptacle

62‧‧‧resistive path

63‧‧‧collimator

64‧‧‧central opening

65a, 65b‧‧‧projection

70‧‧‧outer surface

71‧‧‧ hole (aperture)

72a, 72b‧‧‧identification means

74a~74f‧‧‧resistive contact circle

76‧‧‧Contact bar

100‧‧‧X-ray tube

102‧‧‧ body

104‧‧‧End window

106‧‧‧Applicator cap

108‧‧‧ impact target (target)

110‧‧‧Anode assembly

112‧‧‧cathode

114‧‧‧radiation detector

116‧‧‧catheter (conduit)

118‧‧‧second conduit

120‧‧‧High voltage cable assembly

122‧‧‧beam hardening filter

124‧‧‧Exit surface

126‧‧‧light/indicator

128‧‧‧collimator receptacle

132‧‧‧collimator

134‧‧‧reflective surface/reflective body

B1, B2‧‧‧beam (beam)

P‧‧‧patient

X‧‧‧central axis

1a is a schematic view showing a mobile X-ray unit according to an embodiment of the present invention; FIG. 1b is a schematic view showing a displaceable panel of a mobile X-ray unit according to an embodiment of the present invention; FIG. 2 is a schematic diagram showing the structure of a mobile X-ray unit according to an embodiment of the present invention; FIG. 3 is a schematic diagram showing the structure of a mobile X-ray unit according to an embodiment of the present invention; A schematic cross-sectional view of an X-ray device of a mobile X-ray unit according to an embodiment; FIG. 4 is a schematic view showing a X-ray device according to an embodiment of the present invention having a device cover of FIG. 3; 1 is a schematic view showing a collimator having an identification device according to an embodiment of the present invention; and FIG. 6 is a schematic view showing a collimator having an identification device according to another embodiment of the present invention; Illustrative of an X-ray tube of another embodiment of the invention Figure 7E-E is a longitudinal cross-sectional view showing an X-ray device of an embodiment; Figure 7F-F shows a cathode as shown in the embodiment of Figure 7E-E; and Figure 8 shows A schematic view of an X-ray tube in accordance with another embodiment of the present invention.

2‧‧‧Base

3‧‧‧flexible cable

4‧‧‧X-ray applicator

4a‧‧‧ articulated arm (articulated displaceable arm)

4b‧‧‧Longitudinal axis

4c‧‧‧Exit window

5‧‧‧Displaceable panel

6‧‧‧Handle

7‧‧‧Display

10‧‧‧mobile X-ray unit

Claims (15)

A mobile X-ray unit includes a base for accommodating a control unit, a power supply and a cooler, and a hinged displaceable arm for supporting an X-ray device, the X-ray device The therapy device is coupled to the base and includes an X-ray tube having a longitudinal axis and including an anode for generating an acceleration field and an impact target for generating an X-ray beam. The shaft is arranged to be substantially parallel to the longitudinal axis of the X-ray tube. The mobile X-ray unit of claim 1, wherein the X-ray device comprises a longitudinal axis, the longitudinal axis of the X-ray tube being substantially parallel to the longitudinal direction of the X-ray device axis. The mobile X-ray unit of claim 1 or 2, wherein the longitudinal axis of the anode, the longitudinal axis of the X-ray tube, and the longitudinal axis of the X-ray device are set to be axis. The mobile X-ray unit of claim 1, wherein the anode includes an exit window for emitting the X-ray beam generated from the impact target, the X-ray tube further comprising A collimator for shaping the generated X-ray beam, the exit window and the collimator being disposed substantially at intervals on the longitudinal axis of the X-ray tube. For example, in the mobile X-ray unit described in claim 4, a distance between the impact target and the collimator is about 4 to 10 cm, more preferably about 5 to 6 cm. The mobile X-ray unit of claim 4, wherein the collimator provides an identification device for generating a signal representative of the collimator in the control unit. The mobile X-ray unit of claim 4, 5 or 6, wherein the collimator is replaceable, the mobile X-ray unit comprising a set of collimators having a corresponding identification device. The mobile X-ray unit of claim 7, wherein the collimator is provided in a chamber having a conductive path, the collimator being provided with the protrusion and the conductive path of the chamber Cooperate to generate the signal. The mobile X-ray unit of claim 8, wherein each collimator has at least one contact pin for contacting at least one of a plurality of contact positions of the mobile X-ray unit. To generate the signal. The mobile X-ray unit of claim 8, wherein each of the conductive paths has a different conductivity value, and the detected conductivity value is provided as the identification feature signal. A method of manufacturing a mobile X-ray unit, the mobile X-ray unit comprising a base for accommodating a control unit, a power supply and a cooler, and further comprising a hinged displaceable arm for supporting An X-ray tube of an X-ray tube having a longitudinal axis and including an anode for generating an acceleration field and an impact target for generating an X-ray beam, the method comprising the steps of: The X-ray treatment device is coupled to the base by a connector including a resilient line; the X-ray tube is configured such that one of the anode longitudinal axes is disposed substantially parallel to the longitudinal axis of the X-ray tube. The method of claim 9, wherein the anode comprises an impact target for generating an X-ray beam, the X-ray tube comprising an exit window and a collimator for forming the impact target The X-ray beam is generated, the method further comprising the steps of: arranging the impact target, the exit window, and the collimator disposed substantially at intervals on the longitudinal axis of the X-ray tube. The method of claim 12, wherein a distance between the impact target and the collimator is about 4 to 10 cm. The method of any one of claims 11 to 13, further comprising the step of: substantially vertically arranging the longitudinal axis of the anode, the longitudinal axis of the X-ray tube, and the X-ray treatment One of the vertical axes of the device. A method for providing an X-ray beam to illuminate a lesion surface by using an X-ray unit, wherein the X-ray unit includes a base for accommodating a control unit, a power supply and a cooler, and further comprising a An articulating displaceable arm for supporting an X-ray device, the X-ray device being coupled to the base and including an X-ray tube having a longitudinal axis and including an anode for generating an acceleration The field and a strike target are used to generate an X-ray beam having a longitudinal axis disposed substantially parallel to the longitudinal axis of the X-ray tube.