JP2021045526A - Medical vehicle - Google Patents

Abstract

To efficiently use CT even in mobile means such as a vehicle by reducing a size and weight of CT and also a stroke for moving a bed.SOLUTION: A body axial direction is orthogonal to an advance direction of a medical vehicle. The medical vehicle has a window for introducing/carrying out a subject to/of a gantry of a CT apparatus on a left side or a right side of the medical vehicle.SELECTED DRAWING: Figure 1

Description

The present invention relates to a medical vehicle having a computer tomography apparatus.

The X-ray computed tomography (CT) is a gantry including a rotating part that rotates around the object to be imaged, and a berth movement that advances or retracts the berth on which the subject is placed so as to pass through the inner circumference of the gantry. It is composed of a device, a slip ring that enables electrical connection with a rotating unit, an operation including an image drawing unit that processes data output from a detector, a monitor unit, and the like. Conventionally, inside the rotating part, a large-area detector composed of an aggregate of a large number of image pickup elements, a circuit board for processing a signal from the detector, and an X at a position facing each other across an image pickup object such as a subject. It has a built-in line generator, cooling fan, high-voltage power supply circuit, etc. In this way, CT is a large, heavy, and expensive diagnostic imaging device, and in addition to the installation cost of the building where the CT body is installed, the power supply, the air conditioning equipment, etc., it is always maintained to maintain the optimum performance of the device. Management costs are also a heavy burden. Therefore, there are various difficulties in moving the CT to change the installation location or using it outdoors. Conventionally, vehicles equipped with an X-ray inspection device or the like are known, but the size of the vehicle itself is unavoidable, and the inspection time becomes long because each subject enters the vehicle and undergoes an inspection. It was difficult to efficiently perform an imaging test on a subject (Patent Documents 1 to 4).

Real Kaihei 1-137464 JP 2002-600 Japanese Patent Application Laid-Open No. 8-127282 U.S. Pat. No. 4,928,283

Conventionally, medical vehicles equipped with X-ray equipment (also called X-ray vehicles) have the primary purpose of screening a large number of subjects, and if any suspicious findings are found, they will be revisited at a specialized hospital at a later date. Alternatively, it is necessary to go to an inspection agency and undergo a detailed inspection. However, for the elderly and those who live in depopulated areas, the fact is that it is extremely time-consuming, physical, or financially burdensome to undergo a detailed examination again. In order to use CT in a means of transportation such as a vehicle, it is important to reduce the size and weight of the CT itself, reduce the space required, and secure a stroke for horizontal movement of the bed. Furthermore, since each subject enters the car and lays down on the bed, a waiting / preparation space for the subjects is required, the examination time per person becomes longer, and CT examinations for a large number of subjects are efficiently performed. Is difficult. Further, in order to expand the room for mounting other medical devices and the like, the problems to be solved are the minimization of the stroke area and the space provided to the subject when using CT, and the rapid processing of the examination.

In recent years, the spread of infectious diseases caused by new viruses and the like has become a worldwide problem. For example, diagnostic imaging equipment is indispensable for early detection of early stage pneumonia. In particular, CT is expected as a means for quickly and quickly identifying pneumonia and other infectious diseases because its examination accuracy is higher than that of conventional chest X-ray examinations. At the same time, the issue of how to protect medical professionals from these unknown infectious diseases has also been highlighted. For example, when a CT examination is performed on a large number of subjects who may be infected with a new virus or the like, there is an extremely high risk of infection by nurses, examination technicians, and the like. As described above, at the same time as increasing or speeding up the number of examinations, protection of medical staff and the like is also an issue to be solved.

First, in order to use CT in a means of transportation such as a vehicle, it is required to reduce the size and weight of the CT body. An X-ray source, a detector, a detector signal processing circuit, an X-ray source drive control circuit, an air cooling fan, etc. are built in the rotating part in the gantry. However, the X-ray source, the X-ray source drive control circuit, the air-cooled fan, etc. are heavy, and the moment of inertia and heavy objects when these are rotated at a speed of 0.5 rotations or more per second on the circumference in the gantry. Minimizing the harmful effects of vibration, noise, etc. associated with rotation is also an issue to be solved.

In addition, there is a problem of an increase in the amount of power used by the CT main body and the amount of power used in air conditioning equipment and the like for coping with heat generation of equipment such as CT. When CT is used in a means of transportation such as a vehicle, it is an essential issue to reduce the amount of power used by CT and the amount of power used for air conditioning equipment or the like for coping with heat generation of the equipment or the like. Further, in order to read the output signal of the detector or the like to the outside, the signal is transmitted / received or the electric power is exchanged by a mechanical contact means called a slip ring. In order to ensure the electrical connection by the slip ring, it is necessary to keep the rotation speed low and reduce the number of output signal lines from the detector. In order to reduce the number of signal lines, a method of serializing a parallel signal and reading it out via a slip ring is adopted. However, since the transmission frequency rises when a large amount of imaging data is serially transmitted, it is necessary to develop a dedicated semiconductor device such as a high-speed line buffer element, and it is inevitable that power consumption and heat generation will increase as the transmission frequency rises. .. In recent years, there has been a shift to a structure that exposes a wide area by a single X-ray pulse irradiation. As a result, on the contrary, the weight of the gantry portion is unavoidably increased due to the increase in size of the X-ray generator. In addition, since it is necessary to expand the light receiving area (that is, the number of slices) in the body axis direction, the light receiving area and the number of pixels of the detector used are increased, and further high-speed and large-capacity data transmission and to an external recording medium are performed. High-speed real-time recording is required. For example, when the number of slices is 64, a data processing speed of 1 Gbytes / sec or more is required. In order to record a large amount of data at high speed in real time, for example, measures are taken to use a combination of multiple hard disks such as RAID (Redundant Arrays of Independent Disks), but the recording speed is about 800 Mbytes / sec. There is a problem that it can be suppressed to the following.

Regarding the above-mentioned power transfer, the power supply to the X-ray source or the like becomes a problem. In recent years, as the slice width has increased, the size of the X-ray source has increased, that is, the amount of current supplied to the X-ray source drive control circuit including the high voltage generation circuit has tended to increase as the tube current increases. As a result, the slip ring needs to pass a large current while sliding against the brush, and the contact surface generates heat, increasing the risk of seizure. Therefore, maintenance such as surface polishing of slip rings and brushes and regular replacement of members is indispensable. However, in order to use CT in vehicles, etc., in addition to making the sleeper and gantry part smaller and lighter, it is possible to easily inspect, repair, replace parts, etc. of the faulty part at the destination, or to use CT regularly. Reducing the maintenance load is also an issue to be solved.

Considering the operation of medical vehicles, it is not always possible to use a stable commercial power source depending on the area where medical activities are carried out, natural conditions, etc., and a stable power supply means of its own and a sufficient power source for conducting medical activities. The vehicle needs to have capacity. In addition, it is necessary to consider that medical vehicles will be used outdoors, and it will be necessary to take measures against fluctuations in temperature and humidity, air pollution, and dust. Alternatively, it should be noted that medical vehicles are used in gymnasiums that have become evacuation centers, hotel lobbies, inside tents, and the like. That is, during medical activities, the medical vehicle itself is not allowed to make noise or emit harmful exhaust gas, for example, to supply electric power. As described above, in addition to miniaturization and low power consumption of the medical vehicle itself, it is also a problem to be solved that a clean power source that enables stable long-term operation and does not generate vibration or noise can be provided.

Furthermore, in recent years, as the opportunities for using X-ray CT and the like have increased, there has been increasing concern about X-ray exposure. Therefore, reducing the amount of X-ray exposure of subjects, CT operators, radiologists, nurses, etc. in CT examinations is also a problem to be solved.

In a medical vehicle having a CT, the stroke area required by the CT is minimized or eliminated to reduce the size of the medical vehicle itself or expand the mounting area of other medical devices and the like. Therefore, the medical vehicle having CT has a light source that rotates around the subject around the body axis direction, the body axis direction is orthogonal to the straight-ahead direction of the medical vehicle, and the left side surface of the medical vehicle. Or, it is a medical vehicle having a window portion on the right side surface for introducing or carrying out a subject or a bed for placing a subject on a CT gantry. Alternatively, a medical vehicle having a CT has a light source that rotates around the subject around the body axis direction, the body axis direction coincides with the straight-ahead direction of the medical vehicle in the horizontal direction, and the CT gantry A medical vehicle having a window on the rear side surface of the medical vehicle for introducing or carrying out the subject or a sleeper on which the subject is placed on the inner circumference of the medical vehicle. Preferably, the shape of the window portion viewed from the body axis direction is circular, and the diameter of the circular window portion is larger than the diameter of the inner peripheral portion and the diameter of the outer peripheral portion when the gantry is viewed from the body axis direction. Make it a small medical vehicle.

Preferably, the medical vehicle has a tubular subject protection portion that continuously penetrates the inner peripheral portion of the gantry from the window portion. Preferably, the medical vehicle has an opening area of the window portion larger than the opening area of the subject protection portion and a space portion having a depth toward the inside of the medical vehicle. Alternatively, the subject protection portion is formed continuously from the window portion, and the end portion of the subject protection portion facing the window portion is closed inside the medical vehicle, or the end portion faces the window portion. The structure is connected to the other window portion formed on the other side surface portion of the medical vehicle at the position. More preferably, it is a medical vehicle in which the subject protection unit blocks the inflow and outflow of outside air between the inside and the outside of the medical vehicle. Further, preferably, it is a medical vehicle in which the gantry is attached at a position near the window portion and at a position where the body axis direction and the direction of the central axis of the window portion coincide with each other.

Preferably, a light source, a light source drive control circuit, a detector, a detector are driven at a position facing the light source across the central axis, and a detector control signal processing for processing the output signal of the detector is performed in the rotating portion inside the gantry. A medical vehicle equipped with a circuit and a CT incorporating a secondary battery for driving these. Preferably, any of the secondary battery, the light source, the detector, and the semiconductor image memory in the rotating portion is a medical vehicle having a cartridge structure. Preferably, the light source is an X-ray light source, and the electron beam generating portion of the X-ray light source is a medical vehicle composed of carbon nanostructures.

Preferably, a light source, a light source drive control circuit, and a secondary battery for driving these are built in the rotating portion inside the gantry, and the entire inner circumference of the annular fixed portion concentric with the rotating portion surrounding the rotating portion. An opening in which a plurality of detectors are mounted on the circumference and faces the light source with the rotation center of the rotating part in between, and the light emitted from the light source is passed through to expose the light receiving surface of the detector. It is a medical vehicle equipped with a CT having a rotating part.

The CT used in a medical vehicle is composed of a gantry having a rotating part that rotates about the body axis direction, a gantry on which the gantry is placed, and a control unit that processes and displays image data obtained from the gantry or operates the CT. Moreover, it has a driving means for moving the gantry in the direction of the central axis with respect to the gantry, and further has a light source in the rotating part, a light source drive control circuit for driving the light source, and a rotating part interface, and the gantry has a host interface. , The structure is such that the rotating part interface and the host interface face each other at a predetermined position within the moving range of the gantry. Preferably, the predetermined position is at the end point of the movement range of the gantry. Further, the rotating unit interface and the host interface are close to each other in the vertical direction and face each other. Alternatively, the rotating unit interface and the host interface are configured to be close to each other in the central axis direction and face each other. Preferably, the rotating part interface and the host interface are electrically connected by mechanical contact at a predetermined position. Alternatively, it is a non-contact interface in which the rotating unit interface and the host interface are close to each other at a predetermined position and electrically connected by the interaction of an electromagnetic field in a non-contact state.

The CT used in the medical vehicle provides a driving means for moving the gantry in the central axis direction inside the gantry. Further, a drive motor for rotating the rotating portion is provided inside the gantry. In addition, a protective cover for preventing the subject or the object to be measured from coming into contact with the gantry during the movement of the gantry is provided on the gantry along the moving direction of the gantry. It has a cradle at a predetermined position on the upper part of the gantry, and a host interface is provided on the cradle. Further, the cradle is provided with an inspection probe for inspecting and calibrating the rotating part or a holding means for holding a standard sample. Alternatively, the cradle has a cooling mechanism for cooling the rotating portion at a predetermined position. Alternatively, when CT is not used, the gantry and the cradle have a mechanism for mechanically holding or fixing the gantry at a predetermined position.

Preferably, a lithium ion battery is used as the secondary battery. Further, a large-capacity semiconductor memory, for example, a dynamic random access memory (DRAM) or a non-volatile memory such as a NAND flash memory is used as the image memory. The light source is an X-ray light source or a near infrared (NIR) light source. Preferably, the light source is an X-ray light source, and the electron beam generating portion of the X-ray light source is formed of carbon nanostructures. The detector is preferably a silicon semiconductor detector, and has a structure in which an AD conversion circuit is formed in the silicon semiconductor detector. Preferably, the detector is a photomultiplier tube type detector, an avalanche diode (APD) type detector, or a photon counting type detector. More preferably, an X-ray shielding optical fiber plate that selectively blocks or transmits X-rays at a position facing the X-ray light source on the upper part of the detector, or an X-ray scintillator on the upper part of the X-ray shielding optical fiber plate Have a laminated structure. Preferably, the silicon semiconductor detector is a CMOS type solid-state image sensor having a back-illuminated structure, and X is used to protect or reduce integrated circuits such as horizontal and vertical scanning circuits and signal readout circuits from X-ray damage. A line shielding member is placed above these integrated circuits.

In CT used for medical vehicles, a plurality of induction coils are arranged along the outer peripheral portion of the rotating portion, and the north and south poles alternate along the circumference of the fixed portion in the gantry that surrounds the rotating portion. Arrange the permanent magnets so that they line up with each other. Preferably, a regenerative braking circuit that converts the kinetic energy of the rotating portion into electrical energy is connected to the induction coil. In addition, an electric double layer capacitor is provided in the regenerative braking circuit. This is a driving method when a regenerative braking circuit is used, and imaging is started after the rotation of the rotating portion is started. Next, imaging of the subject by X-ray irradiation is started. The digital data obtained from the detector array is recorded in the image memory in real time. After the imaging is completed, the rotational kinetic energy of the rotating portion generates a counter electromotive force in the induction coil and recovers it as electrical energy, and the rotational motion slows down while charging the capacitor or the secondary battery. Next, the data recorded in the image memory is read from the rotating unit interface via the host interface. In parallel, the secondary battery is charged, and a series of sequences are completed to enter the standby state. Alternatively, in a modified example of the driving method when a regenerative braking circuit is used, when the rotation speed of the rotating portion during CT imaging is n1 and the rotation speed of the rotating portion during non-CT imaging is n2, CT The rotation speed n2 of the rotating portion is increased from n1 (n2> n1) at the time of non-imaging, and this is a CT driving method used in a medical vehicle for charging the secondary battery.

In CT used for medical vehicles, the rotating part inside the gantry is composed of two parts, one rotating part is equipped with a timing belt, and the other rotating part is mechanically connected to one rotating part by a ratchet structure. The structure should be linked. A claw is attached around one rotating portion, and when it rotates clockwise, it is caught in a groove on the inner circumference of the other rotating portion, and torque can be transmitted to the other rotating portion. On the contrary, when one rotating portion rotates counterclockwise, the claw cannot transmit torque over the groove on the inner circumference of the other rotating portion, and the other rotating portion idles. This is a driving method when a ratchet structure is used. After one rotating portion starts rotating in a direction in which torque is applied to the other rotating portion, imaging by X-ray irradiation is started. The digital data obtained from the detector array is recorded in the image memory in real time. When the rotational torque of one rotating portion decreases or stops after the completion of imaging, the other rotating portion is released from the coupling with the one rotating portion and idles. By the regenerative brake in the other rotating portion, the rotational kinetic energy generates a counter electromotive force in the induction coil and recovers it as electric energy, and the rotational movement of the other rotating portion is decelerated while charging the capacitor or the secondary battery. After the rotation of the other rotating unit is stopped, the data recorded in the image memory is read from the rotating unit interface via the host interface. In addition, the secondary battery is charged in parallel, and a series of sequences are completed to enter the standby state.

The CT used in a medical vehicle has a cartridge structure in which any one of an X-ray generator, a detector array, an image memory, and a secondary battery incorporated inside a rotating portion in a gantry can be attached and detached. Further, the structure is such that the first X-ray generator, the second X-ray generator, and the first detector array and the second detector are provided at positions facing each other in the central direction thereof. The first detector array and the second detector array are shifted in the Z-axis direction. Alternatively, the first X-ray generating unit and the second X-ray generating unit irradiate X-rays at the same time or with a time lag. Further, the first X-ray generator and the second X-ray generator have different tube voltages (wavelengths).

In CT used in medical vehicles, a control signal for controlling the movement of the gantry or the sleeper in the axial direction, or the imaging operation of the gantry, or a wireless interface for transmitting and receiving image data by wireless communication is provided with a CT control unit. Install between the gantry, the gantry, or the cradle.

The CT used in the medical vehicle has a structure in which two gantry parts are mounted on a gantry. In addition, the cradle portion has a donut-shaped hollow structure so that the subject and the sleeper can pass through. The plurality of gantry units are a combination of any of an X-ray CT examination gantry, a positron emission tomography (PET) examination gantry, and a near-infrared diffused light imaging gantry.

A medical vehicle in which the power source for driving the CT is a fuel cell using hydrogen as a raw material. Preferably, the medical vehicle is an electric vehicle that operates by using a fuel cell as a power source, and the fuel cell is a medical vehicle that drives a CT device. Preferably, the medical vehicle is a medical vehicle in which a vehicle regenerative braking circuit for converting kinetic energy during deceleration of the medical vehicle into electrical energy and charging the secondary battery inside the CT is connected to the secondary battery. In addition, medical treatment that uses the electromotive force generated by the vehicle regenerative braking circuit that converts the kinetic energy during deceleration of a moving vehicle into electrical energy to charge the secondary battery inside the rotating part of the CT when it is stationary. The driving method of the vehicle.

According to the present invention, it has become easy to miniaturize a medical vehicle equipped with CT by minimizing or eliminating the stroke region required by CT. It has become easier to secure the space required when using CT, for example, the stroke for horizontal movement of the bed, outside the medical vehicle, and quick and efficient inspection has become possible. Even if a stable commercial power source cannot be obtained, it has become possible to continue medical activities by using its own stable power supply means. By providing a clean power source, stable and long-time CT operation is possible without generating noise for power supply or emitting harmful exhaust gas. Therefore, medical activities in a closed or anti-closed space such as a gymnasium that has become an evacuation center, a hotel lobby, or the inside of a tent have become easier. Imaging diagnosis by CT is not only effective for early detection of serious diseases such as cancer, heart disease, and cerebrovascular disease, but also some lesions may be observed in the images taken for other purposes. By utilizing AI and high-speed communication methods, it has become possible to detect such various abnormalities that may occur in the human body from a wide range of viewpoints even in remote areas without overlooking them. By using the medical vehicle of the present invention and combining a high-speed communication method such as 5G and image diagnosis utilizing AI (artificial intelligence), a one-stop medical service can be realized even in a remote place or a disaster site.

(A) is a side view of the medical vehicle 100 according to the embodiment as viewed from the Z-axis direction. (B) is a plan view of the medical vehicle 100 looking down from the Y-axis direction. (C) is a plan view for explaining the arrangement of the CT 61 when viewed from the rear portion (X-axis direction) of the medical vehicle 100. (D) is a cross-sectional view of the CT61 mounted on the medical vehicle 100 as viewed from the Z-axis direction. (A) is a side view of the medical vehicle 200 according to the embodiment as viewed from the Z-axis direction. (B) is a plan view of the medical vehicle 200 as viewed from the Y-axis direction. (C) is a plan view for explaining the arrangement of the CT63-1 when viewed from the rear part (X-axis direction) of the medical vehicle 210. (A) is a cross-sectional view for explaining the arrangement of the CT65 when the medical vehicle 300 according to the embodiment is viewed from the rear (X-axis direction). (B) is a cross-sectional view illustrating the arrangement of CT67-1 in particular when the medical vehicle 310 according to the embodiment is viewed from the rear (X-axis direction). (C) is a plan view of the medical vehicle 310 looking down from the Y-axis direction. (D) is a cross-sectional view illustrating the arrangement of the CT67-2 when viewed from the rear portion (X-axis direction) of the medical vehicle 320. (A) is a side view of the medical vehicle 400 according to the embodiment as viewed from the Z-axis direction. (B) is a plan view when viewed from the rear portion (X-axis direction) of the medical vehicle 400. (C) is a plan view of the medical vehicle 410 looking down from the Y-axis direction. (A) is a side view of CT61-2 as viewed from the X-axis direction. (B) is a plan view of the CT apparatus 61-2 looking down from the Y-axis direction. (C) is a plan view of a main part of CT61-2 as viewed from the Z-axis direction. (A) is a side view of CT63-2 as viewed from the X-axis direction. (B) is a block diagram for explaining the circuit configuration of the wireless power feeding part in the non-contact interface part (10 and 12). (A) is a plan view for demonstrating an example of the internal structure of the rotating portion 23 in CT according to an Example. (B) is a circuit block diagram for explaining a detector and its peripheral circuits. (C) is a circuit block diagram for explaining the inside of the rotating portion 23, particularly the X generating portion and the high voltage drive circuit. (A) is an XY plan view seen from the Z-axis direction for explaining another structure of the gantry portion suitable for CT61 according to the embodiment. (B) is a cross-sectional view taken from the X-axis direction for explaining another structure of the gantry portion suitable for CT61. (C) is an enlarged view of a portion A surrounded by a broken line in (a). (D) is a plan view when the opening direction is viewed from the X-ray source 25 m in order to explain the opening 28 formed in the rotating portion 23-2, and is a detection arranged in the fixed portion 24 in the opening. A part of the vessel unit 30 is visible. FIG. 8A is a plan view of the CMOS type solid-state image sensor 30-1, which is a modification of the detector unit 30 shown in FIG. (B) is a plan view when the CMOS type solid-state image sensor 30-2, which is also another suitable detector unit 30, is arranged so as to face each other so that the light receiving regions are in close contact with each other. (C) is an enlarged view for explaining the cross-sectional structure of the CMOS type solid-state image sensor 30-2 in (b). (A) is a side view of CT63 used in the medical vehicle 200 according to the embodiment as viewed from the X-axis direction. (B) is a plan view also seen from the body axis direction. (C) is an enlarged view of the portion B surrounded by the broken line in (a). (D) is a cross-sectional view of the rotating portion 23 according to the embodiment as viewed from the X-axis direction. (E) is a plan view of a main part for explaining a configuration according to a modified example of the rotating portion 23 when viewed from the body axis direction. (A) is a plan view for explaining the structure of the rotating portion 23 of the CT according to the embodiment, particularly the modified example of the gantry 5. (B) and (c) are partially enlarged views for explaining electromagnetic induction in the outer circumference of the rotating portion 23 in the broken line portion 39 in (a) and the inner circumference of the gantry 5 surrounding the rotating portion 23. (D) is a circuit block diagram for explaining the regenerative brake 50 inside the rotating portion 23. (A) is a plan view for explaining the internal structure according to another embodiment of the gantry part 5. (B) is a partially enlarged view for explaining an example (broken line portion 39R) of the ratchet mechanism in the rotating portions 23-1 and 23-2 shown in (a). (C) is a flowchart for explaining a driving method of a CT device when a regenerative brake, a ratchet mechanism, or the like is used. (A) is a block diagram for explaining the power source configuration in the medical vehicle 500 according to the embodiment. (B) is a schematic view of the medical vehicle 510 according to the modified example of the medical vehicle 500 according to the embodiment. (C) is a flowchart for explaining the operation of the medical vehicle 500 and the operation process of the CT.

In the present invention, the straight direction of the vehicle is defined as the X-axis, the height direction of the vehicle, that is, the vertical direction is defined as the Y-axis, and the left-right direction with respect to the traveling direction of the vehicle, that is, the direction orthogonal to the X-axis and the Y-axis is defined as the Z-axis. .. The medical vehicle 100 according to the embodiment will be described below with reference to FIGS. 1 (a) to 1 (d). FIG. 1A is a side view of the medical vehicle 100 according to the embodiment as viewed from the Z-axis direction. On the side surface of the vehicle, there is a subject window portion 20 into which a sleeper on which a subject such as a human body is placed is inserted. In CT61, the body axis direction of the gantry portion (not shown) coincides with the Z axis direction. In this embodiment, after the sleeper (3) on which the subject is placed is guided onto the sleeper support portion 3S, imaging is performed while moving the gantry in the Z-axis direction. Alternatively, as will be described later, CT may be used to image a fixed gantry while moving the subject in the Z-axis direction. The medical vehicle 100 is provided with a solar panel 71 and stairs 18 for entering and exiting the vehicle in order to utilize natural energy. FIG. 1B is a plan view of a main part viewed from the Y-axis direction. As shown in the figure, the medical vehicle 100 uses a simple mobile sleeper 62 called a stretcher with the subject lying on the sleeper 3 from the side surface of the vehicle, and the sleeper support portion 3S of the CT61 is used. Can be led to the top of. In this embodiment, the cradle 9-1 described later is provided. The cradle is a part that stands upright from the floor surface, wall surface, pedestal, etc., and is a space in which the gantry 5 stands by, and is a host interface that is electrically connected to the rotating portion interface of the rotating portion 23 inside the gantry 5. Etc. When the CT 61 is not used, for example, when the medical vehicle 100 is moving, the sliding door 52 for shielding the subject window 20 is provided. The medical vehicle 100 includes a data processing room, a power control room, other testing equipment room, a biochemical testing room, an examination room, a waiting room or a changing room (16-1 to 16-6), and an in-vehicle passage (16P). Have. As described above, since the stroke region required by the CT 61 is not inside the medical vehicle 100 but outside the medical vehicle 100, the medical vehicle 100 is not enlarged or the space inside the vehicle is used for other purposes. It can be used effectively. As will be described later, inside the gantry 5, there is a light source unit (X-rays, etc.) that can rotate around the body axis direction, and an operation / control unit and a display (monitor) unit (not shown) are inside the vehicle. It is provided in. That is, a tomographic image or the like reconstructed by an image drawing circuit, software, or the like is displayed on the monitor. As will be described in detail below, a wired or wireless electrical connection means for exchanging an electric signal or electric power between the rotating portion in the gantry and the gantry supporting the rotating portion is provided on the rotating portion side in the gantry and the gantry. During the imaging, only the gantry 5 moves in the Z-axis direction, and the subject is stationary on the sleeper 3 together with the sleeper 3, so that a robust and precise subject movement control sleeper is not always required. Therefore, the medical vehicle 100 itself can be easily reduced in size and weight. Further, even if the imaging scanning speed in the body axis (Z-axis) direction of the gantry is increased, there is an effect that the physical / mental load and anxiety of the subject can be avoided.

FIG. 1C is a cross-sectional view of a main part for explaining the structure of the medical vehicle 100, particularly when the CT61 is viewed from the rear of the vehicle in the X-axis direction. The sleeper 3 on which the subject is placed is carried into the CT 61 from the subject window 20. In this case, the stretcher 62 may hold the sleeper 3, but in order to hold the subject more stably, the CT61 may be provided with the sleeper holding plate 3S in advance. As described above, the gantry 5 has a rotatable light source or the like inside thereof, and takes a tomographic image of the subject while moving in the Z-axis direction. In this way, since the gantry 5 moves along the subject, the subject protection member 51 that prevents the gantry from coming into contact with the subject is attached so as to penetrate the inner peripheral portion of the gantry 5. Further, at the other end of the moving range of the gantry 5, there is a cradle 9-1 described later, which can be electrically or mechanically coupled to the gantry 5. Although this figure shows an example of being transferred from the lower body of the subject (person) to the inside of the CT61, it may be guided from the head to the CT61. This is because in many cases, the inspection target is the upper body such as the head and internal organs, and it is not always necessary to image the whole body. Therefore, the dimension of the CT61 in the Z-axis direction can be shortened to, for example, about 1 m (meter), and the space occupied by the CT61 in the medical vehicle 100 can be reduced. FIG. 1D is an enlarged view of a main part of the CT61 as viewed from the Z-axis direction. The subject protection member 51 is circular because it is located on the inner peripheral portion of the gantry 5. Since the gantry 5 is supported by the gantry 7 and moves, the gantry 5 is attached to the gantry moving carriage 11. In this embodiment, the gantry 7 is attached to the side surface 55-3 of the medical vehicle 100, but it may be attached on the floor surface (55-1) as described later.

The medical vehicle 200 according to the embodiment and the medical vehicle 210 according to the modified example will be described below with reference to FIGS. 2 (a) and 2 (c). FIG. 2A is a side view of the medical vehicle 200 according to the embodiment as viewed from the Z-axis direction. However, unlike the case of FIG. 1A, the front of the medical vehicle 200 is to the right in the drawing. On the side surface of the vehicle, there is a subject window 20 for inserting a sleeper (3-1) on which a subject such as a human body is placed along the upper part of the sleeper holding plate 3S inside the CT63. In CT63, the body axis direction of the gantry coincides with the Z axis direction. In this embodiment, a case where imaging is performed while moving the bed (3-1) on which the subject is placed with the gantry portion fixed will be described. FIG. 2B is a plan view of a main part of the medical vehicle 200 as viewed from the Y-axis direction. In this embodiment, the subject window portions 20 are provided on the left and right side surfaces of the medical vehicle 200, and a funnel-shaped subject protection member 53 is attached between the subject insertion portion and the subject window portion 20 of the CT63. As will be described later, it prevents outside air from entering the inside of the medical vehicle 200. From one side of the vehicle of the medical vehicle 200, the subject is guided into the CT63 by the transport unit 3-2 of the sleeper moving device in a state of lying on the bed 3-1 of the sleeper moving device. That is, the stroke region required by the CT 63 is not inside the medical vehicle 200, but outside the medical vehicle 200. In this embodiment, the gantry 5 is fixed to the substantially central portion of the medical vehicle 200 in the Z-axis direction. Inside the gantry 5, there is a rotatable rotating unit, and an operation / control unit and a display (monitor) unit (not shown) are provided in the vehicle. That is, a tomographic image or the like reconstructed by an image drawing circuit, software, or the like is displayed on the monitor. Further, in the medical vehicle 200, similarly to the medical vehicle 100, spaces (16-1 to 16-6, and 16P) for other purposes, stairs 18, and the like are arranged. Further, when the CT63 is not used, for example, while the medical vehicle 200 is running, the doors 52-1 and 52-2 that can be opened and closed are provided to shut the CT63 from the outside of the vehicle. With this structure, the subject can be carried in or out from either the left or right side of the medical vehicle 200.

FIG. 2C is a cross-sectional view of a main part for explaining the structure of the medical vehicle 210, particularly when the CT63 is viewed from the rear of the vehicle in the X-axis direction. From the subject window portion, the sleeper 3-1 on which the subject is placed passes through the gantry 5 inside the CT63 while moving on the sleeper support portion 3S by the transport portion 3-2 of the sleeper moving device. The gantry 5 has a rotatable light source or the like inside thereof, and takes a tomographic image of the subject while the sleeper 3-1 is moving in the Z-axis direction. In this embodiment, the gantry 5 has a structure fixed to the floor surface 55-1, and a subject protection member 51 is attached so as to penetrate the inner peripheral portion of the gantry 5. Further, at the left and right ends of the subject protection member 51, a conical or funnel-shaped subject protection member 53 plays a role of continuously connecting the window portion and the subject protection member 51. With this structure, the inside of the medical vehicle 210 can be shielded from the outside of the medical vehicle 210, so that fluctuations in the temperature and humidity inside the CT63 and the vehicle can be suppressed, or droplets emitted from the nose or mouth of the subject or dust from the outside can be suppressed. Can be prevented from entering the vehicle. Further, as shown in the figure, transport portions 3-2 of the sleeper moving device are arranged on the left and right side surfaces of the medical vehicle 210, and the subject carried in from one subject window portion is placed on the opposite side of the subject window portion. Can be carried out from. In this way, the subject can be carried in from one side and carried out from the other side, and is suitable for, for example, when a large number of subjects are continuously inspected. Conventionally, in order to perform such continuous inspection, it was necessary to substantially double the stroke area corresponding to the carry-in side and the carry-out side in the vehicle, but this structure requires the stroke area itself. A large number of subjects can be efficiently tested without doing so.

The medical vehicle 300 according to the embodiment and the medical vehicles 310 and 320 according to the modified example will be described below with reference to FIGS. 3 (a) to 3 (d). FIG. 3A is a cross-sectional view of a main part of the medical vehicle 300 according to the embodiment as viewed from the rear X-axis direction. As shown in the figure, on one side surface of the medical vehicle 300, there is a subject window portion 20 for loading and unloading the subject into the CT65, a funnel-shaped subject protection member 53 and a subject protection member 51 are attached, and further, a subject. The end portion 51-2 of the protective member 51 on the opposite side facing the subject window portion has a shape closed with respect to the inside of the vehicle. Further, the gantry 5 of the CT65 is fixed in the vicinity of the subject window portion, and the subject is lying on the bed 3-1 of the bed moving device, and the CT65 is operated by the transport unit 3-2 of the bed moving device. Is led to. Therefore, the stroke region required by the CT65 is not inside the medical vehicle 300 but outside the medical vehicle 300. Further, since the space occupied by the gantry 5 is fixed in the vicinity of the subject window portion 20, the space inside the vehicle can be used more effectively. As described above, if the dimension of the CT65 in the Z-axis direction is, for example, a length sufficient for photographing the upper body, the space occupied by the CT65 in the vehicle can be further reduced.

FIG. 3B is a cross-sectional view of a main part of the medical vehicle 310 according to the embodiment as viewed from the rear X-axis direction. As shown in the figure, there is a subject window portion 20 on one side surface portion of the medical vehicle 310, and the shape of the subject window portion 20 viewed from the X-axis direction is, for example, a vertically long rectangle and its opening area. Is larger than the area of the opening of the subject protection member 51. That is, it has a space portion 57 indicated by a shaded portion having a depth toward the inside of the vehicle, and the height (h), width (w), and depth (d) of the space portion 57 are determined by the subject (person) himself / herself in the sleeper 3. It is preferably large enough to sit on top and lie down. For example, the height h and the depth d in this figure are in the range of 120 cm to 200 cm and 50 cm to 100 cm, respectively. Similar to CT63, CT67-1 has a structure in which a subject lies on the bed 3, slides on the bed support 3S, and then stands still, and the gantry 5 takes an image while moving in the Z-axis direction. The moving distance of the gantry 5 in the Z-axis direction may be the upper body, for example, about 100 cm to 150 cm. With this structure, the stroke region required by the CT67-1 is outside the medical vehicle 310, and the subject can ride on the bed and inside the CT67-1 without using a subject moving means such as a stretcher. Can be sent. FIG. 3C is a plan view of a main part of the medical vehicle 310 as viewed from the Y-axis direction. The width w of the region 57 indicated by the shaded area is preferably in the range of 150 cm to 200 cm, for example, to the extent that the subject can easily sit on the bed 3. It should be noted that preferably, the wall surface of the space portion 57 is formed integrally with the subject protection member 51 to prevent outside air from entering the inside of the medical vehicle 310.

FIG. 3D is a cross-sectional view of a main part of the medical vehicle 320 according to the embodiment as viewed from the rear X-axis direction. As shown in the figure, there are subject window portions 20 on both the left and right side surfaces of the medical vehicle 320, and like the medical vehicle 310 described above, the opening seen from the X-axis direction is larger than the opening of the subject protection member 51. It has space parts 57 on the left and right toward the inside of the vehicle. The height, width, depth, etc. of the space portion 57 are such that the subject (person) can lie down on the sleeper 3-1 by himself / herself. In this embodiment, the gantry 5 is located at the center of the vehicle in the Z-axis direction and is fixed to the floor 55-1 of the vehicle. Since the gantry 5 does not move, the length of the subject protection member 51 in the Z-axis direction can be shortened, and at the same time, the volume of the space portion 57 can be expanded. Further, in order to expand the stroke region outside the vehicle, the auxiliary plate 59 attached to the vehicle body may be rotated by 90 degrees as shown in the figure. In this embodiment, the subject is guided to the CT67-2 by the small transport unit 3-3 of the bed moving device while lying on the bed 3-1 of the bed moving device. With this structure, CT inspection can be performed from either the left or right side, and the stroke area is not reduced or the stroke area itself is not required. Further, similarly to the medical vehicle 210, it is possible to efficiently perform a CT examination on a large number of subjects while continuously moving the subjects in one direction.

The medical vehicles according to the examples 400 and 410 will be described below with reference to FIGS. 4 (a) to 4 (c). FIG. 4A is a side view of a main part of the medical vehicle 400 according to the embodiment as viewed from the Z-axis direction. The CT69-1 is arranged in the vehicle so that the body axis direction of the gantry 5 coincides with the X-axis direction, and there is a subject window portion on the rear side surface portion of the vehicle into which a sleeper on which a subject such as a human body is placed is inserted. .. In this embodiment, the sleeper 3-1 on which the subject is placed is introduced into the CT69-1 by the transport unit 3-2 of the sleeper moving device, and the gantry 5 attached to the vicinity of the side surface of the rear part of the vehicle in the meantime. The image is taken by. Further, in order to match the height of the CT69-1, a horizontal stroke region is created by rotating the auxiliary plate 18f previously attached to the vehicle body by 90 degrees using the wire 18a, as shown in the figure, and further via the slope 18S. On top of that, the transport unit 3-2 of the sleeper moving device can be introduced. FIG. 4B is a plan view of the rear portion of the medical vehicle 400 as viewed from the X-axis direction. A funnel-shaped subject protection member 53 is attached to the subject window portion 20. It also has an openable door 52-3 for entering the vehicle. In this way, since the stroke region required by the CT69-1 is not inside the medical vehicle 400 but behind and outside the medical vehicle 400, the space inside the vehicle can be effectively utilized without increasing the size of the medical vehicle 400. In addition, a stroke area can be easily secured outside the vehicle even in a narrow place, a passage, or the like.

FIG. 4C is a plan view of a main part of the medical vehicle 410 according to a modified example of the medical vehicle 400 as viewed from the Y-axis direction. In this embodiment, the gantry 5 has a structure in which an image is taken while moving in the body axis, that is, the X-axis direction with respect to the subject, and as described above, the subject can be introduced from outside the company by a stretcher 62 or the like. .. Further, in the medical vehicle 410, the CT69-2 can be used even when the subject window portion 20 is shielded. That is, in CT69-2, the side surface portion of the subject protection member 51 on the vehicle interior passage (16P) side, which is not shown, is openable and closable, and as shown by the white arrow, it is glued from the vehicle interior onto the sleeper 3. , Can lie down. With this structure, in addition to the inspection method to prevent the influence of the outside air and infection from the patient by guiding the subject from the outside of the vehicle using a stretcher 62 etc., if there is no such concern or the subject enters the vehicle and conducts the inspection. The structure is such that it can be used even when the benefits are greater.

The structure of the CT suitable for the medical vehicle 100 (FIG. 1 and the like) according to the embodiment described above will be described below. For the sake of simplification of the description, in FIGS. 5A to 5C, CT61-2 having a pedestal 7 on a more general horizontal floor surface will be described as an example. FIG. 5A is a side view of a main part of CT61-2 as viewed from the X-axis direction. The CT61-2 is derived from a gantry moving trolley 11, a gantry 5, etc., which incorporates a gantry 7, a gantry support (not shown) that supports the gantry, a cradle 9-1, and wheels 15 that facilitate movement in the Z-axis direction. It is configured. When CT imaging is not performed, the cradle 9-1 can be retracted and fixed in the gantry storage portion 37 shown by the broken line, so that the gantry 5 can be protected from vibration or the like while the medical vehicle is moving. Preferably, a cylindrical subject protection member 51 is arranged inside the gantry 5. Further, it may have a sleeper support portion 3S. This is to guide and hold the subject placed on the simple sleeper on the sleeper support portion 3S. Inside the gantry 5, there is a rotatable rotating portion (23) described later, and the rotation central axis 1 thereof is shown in the drawing. It should be noted that there is an operation / control unit and a display (monitor) unit (not shown), and a tomographic image or the like reconstructed by an image drawing circuit, software, or the like is displayed on the monitor. During the imaging, only the gantry 5 moves in the Z-axis direction, and the subject is stationary on the bed. Therefore, in this structure, a robust and precise subject movement control means is not required, and the CT itself can be made smaller and lighter. Further, even if the scanning speed in the body axis (Z axis) direction of the gantry is increased, there is an effect that the physical / mental load and anxiety of the subject can be avoided. The gantry 5 may be towed from the cradle 9-1 side as a moving means for moving the gantry 5 in the Z-axis direction.

FIG. 5B is a plan view of a main part of CT61-2 as viewed from the Y-axis direction. Two rails 13 for moving the gantry are provided on the upper part of the gantry 7 so that the gantry 5 moves on the gantry 7. If the gantry moving rail 13 and the wheels 15 are made of a conductive material such as metal, power is supplied to the drive motor (17) inside the gantry moving carriage 11, or a control signal is sent to and from the gantry moving carriage 11. Etc. can be exchanged. As described above, the host interface 2-1 which is an electrical connection means for exchanging electric signals or electric power between the rotating portion 23 and the gantry 7 in the gantry is set on the upper part of the gantry, that is, within the movement range of the gantry 5. It is arranged at a position, for example, at the end point of the movement range of the gantry 5. Since the gantry 3 can be removed from the gantry 7 by removing the sleeper support 3S, maintenance and replacement of the gantry 5 is easy, and a gantry equipped with light sources having different imaging characteristics, for example, different light source energies (wavelengths). It can also be replaced with.

FIG. 5C is a plan view of a main part of CT61-2 as viewed from the Z-axis direction. Inside the gantry 5, a rotating portion 23 that rotates around the rotation center shaft 1 is attached via a bearing (not shown) or the like. Further, a timing belt 21 for rotating the rotating portion 23 is attached to the gantry rotating portion drive motor 19 inside the gantry moving carriage 11. Further, since the rotating unit 23 has the rotating unit interface 2-2, the rotating unit 23 can be electrically connected at a position facing the host interface 2-1 when the rotating unit 23 is stationary. It should be noted that preferably, a position sensor or the like (not shown) using a Hall element or the like can be used in order to stop the host interface 2-1 and the rotating unit interface 2-2 at opposite positions. Further, a gantry moving carriage drive motor 17 for moving the gantry 5 in the Z-axis direction is provided inside the gantry moving carriage 11. The power supply for driving can be supplied from the gantry moving rail 13 as described above, but a secondary battery can also be built in the gantry moving carriage 11. As will be described later, the structure may be such that the host interface is located in the cradle 9-1 and the gantry 5 is electrically connected to the rotating portion interface in a state of approaching or being coupled to the cradle 9-1.

Non-contact power supply between the host interface on the cradle side and the rotating unit interface in the gantry, and other transmission and reception of electric signals will be described with reference to FIGS. 6A and 6B. FIG. 6A is a CT device (63-3) in which the gantry 5 moves in the body axis direction with respect to a stationary subject as described above, and is the same as in the case of the medical vehicle 200. The structure has subject windows on both the left and right sides of the vehicle. Further, the cradle 9-3 and 9-4 are provided in the vicinity of the left and right subject window portions 20. Therefore, one gantry can be electrically coupled to both the left and right cradle, but in this embodiment, a case where two gantry 5-1 and 5-2 are provided will be described. As shown in the figure, there are subject window portions 20 on the left and right side surfaces (55-3, 55-5) of the vehicle, and a funnel-shaped subject protection member 53 is attached to the subject protection member 51 which has already been described. On the other hand, they are continuously combined. Therefore, the subject protection member 53 penetrates the insides of the cradle 9-3 and 9-4 in the Z-axis direction. The left and right cradle 9-3 and 9-4 have a non-contact host interface 10, and the gantry 5-1 and 5-2 have a non-contact rotating part interface 12, and the gantry and the rotating part face each other. The structure is close to each other. As described above, in order to stop the host interface 10 and the rotating unit interface 12 at opposite positions, a position sensor or the like using a Hall element can be used. By using a CT having two gantry 5-1 and 5-2, for example, multi-image diagnosis for different medical fields such as orthopedics, cardiology, and gastroenterology and different light source energies becomes easy. .. Further, one gantry can be used as a PET gantry or a gantry using near infrared light as a light source.

FIG. 6B is a block diagram for explaining an example of a circuit configuration related to electromagnetic induction type wireless power feeding in the non-contact interface units (10 and 12). As shown in the figure, the circuit configuration on the host interface side (10) consists of an AC / DC converter (10-3) that converts commercial power (10-2) to direct current, and a high-frequency inverter (10-) that outputs high-frequency square waves. 4), it is connected to the primary coil L1 (10-1) via a waveform conversion circuit (10-5) that converts this into a sinusoidal wave, an insulated transformer (10-6) for ensuring safety, and the like. On the other hand, the secondary coil L2 (12-1) is loaded with a light source, a secondary battery charging circuit, etc. via a rectifying smoothing circuit (12-4) that returns high frequencies to direct current, a backflow blocking diode ((12-3), etc.). It is connected to (12-2). On the other hand, for transmission / reception of control signals or image data, for example, a wireless communication method (not shown) based on near-field magnetic field coupling is used. In addition, it has rapidly become widespread in recent years. It is also possible to transmit high-speed, large-capacity CT image data using a high-speed, large-capacity communication method (for example, 5G) that is being developed. The data transfer speed can be increased by giga (G) bits / second or more. This is because it is possible. The wireless power supply and the wireless communication may be performed by using the same coil or antenna.

The structure of the CT, particularly the structure of the rotating portion 23, will be described in detail with reference to FIG. 7. FIG. 7A is a plan view of a main part viewed from the Z-axis direction for explaining the internal structure of the rotating portion 23 inside the gantry 5. Inside the rotating unit 23, a light source such as an X-ray generating unit 25, a high voltage control circuit 29, a detector array 31, a detector peripheral circuit 33, an image memory 35, a secondary battery 27, and a rotating unit interface 2-2 are provided. Have. That is, the X-ray beam 26 emitted from the X-ray generating unit 25 passes through the subject (not shown) placed on the bed 3 and reaches the detector array 31. A weight balance adjusting unit for adjusting the weight balance during rotation of the rotating unit may be provided. Preferably, an X-ray generator using a carbon nanomaterial such as carbon nanotube (CNT) as a field electron emission source is used for the X-ray generator 25. Since carbon nanomaterials are used as the cold cathode material, preheating is not required, and compared to the case of using conventional X-ray tubes, it is possible to reduce the size and power consumption, and the high voltage control circuit 29 can be made smaller. This is because the cooling fan can be downsized or the cooling fan itself can be eliminated. In this embodiment, the structure in which the detector array 31 is built in the rotating portion 23 has been described. However, as will be described later, the detector array 31 is not inside the rotating portion 23 but the rotating portion 23. The structure may be arranged over the entire inner circumference of the surrounding gantry 5 (FIG. 8 and the like).

FIG. 7B is a circuit block diagram for explaining the inside of the rotating portion 23 in FIG. 7A, particularly the detector 31 and its peripheral circuit 33. As shown in FIG. 7B, the peripheral circuits 33 in FIG. 7A include a detector drive control circuit 41, a signal amplification / analog-to-digital (AD) conversion circuit 43, a signal scanning / control circuit 45, and digital signal processing. A circuit 47, a parallel serial conversion circuit 49, and the like are included. As shown in the figure, a plurality of detector units 30 are regularly arranged in an arc shape or in the Z-axis direction in order to increase the number of slices in the detector array 31. The detector unit 30 includes, for example, a small electron multiplier type detector (for example, "micro PMT element" manufactured by Hamamatsu Photonics Co., Ltd.), an amplification type detector using an avalanche effect (APD), and a photomultiplier type detector. Etc. can be used. Further, since a CMOS type or CCD type detector in which an analog-to-digital (AD) conversion circuit is turned on-chip can be used, high-speed and low-noise signal readout can be realized. Since these detector units have high sensitivity or low noise, they do not necessarily require a large area detector unit having a large number of slices, for example, a large area detector in which a TFT is laminated on a glass substrate. Therefore, the amount of X-ray irradiation (exposure) is reduced, or high-speed scanning in the Z-axis direction by short-time pulse irradiation becomes easy. Further, as will be described later, since it is not necessary to expand the X-ray irradiation area, it is not necessary to increase the voltage and current values required for the X-ray generating portion. Further, in addition to weight reduction by thinning the rotating portion 23 in the Z-axis direction, it is possible to improve the stability and durability of the carbon nanomaterial used as a field electron emission source in particular.

The detector signal output from the detector array 31 is converted into digital data (for example, 16 bits) by the signal amplification / AD conversion circuit 43, and sent to the digital signal processing circuit 47 via the signal scanning / control circuit 45. The necessary image processing is added. An image memory 35 is built in the rotating unit 23 in order to directly record the image data sent from the digital signal processing circuit 47. Since parallel recording can be performed directly in the image memory 35 via the bus line 38 without parallel serial conversion, high-speed writing becomes possible. Although a magnetic recording medium can be used as the image memory 35, a semiconductor image memory such as a DRAM or a NAND flash memory is suitable from the viewpoint of recording speed and reliability. On the other hand, when the image data is read from the image memory 35 after the end of imaging and after the rotation of the rotating unit 23 and the movement of the gantry 5 are stopped, it is not necessary to read the image data in real time unlike the time of imaging. Therefore, the parallel serial conversion circuit 49 Therefore, it may be output to the host interface 2-2 as serial data. Serialization also has the effect of reducing the number of terminals in the host interface 2-2. In the electrical connection means including the host interface 2-2 and the rotating portion interface 2-1, there are a plurality of connectors 6 inside the rotating portion interface 2-1 of the rotating portion 23, and the shape thereof is a concave receiving structure. .. On the other hand, there are a plurality of connectors 4 on the side of the host interface 2-2 on the upper part of the gantry 7, and the shape thereof is convex. Electrical connection is possible by inserting the connector 4 into the connector 6. In this way, the image data recorded and accumulated inside the rotating unit 23 when it is stationary is read from the rotating unit interface 2-1 to the host interface 2-2 without using the slip ring which is a mechanical electrical contact. Therefore, the above-mentioned adverse effect when using the slip ring can be eliminated, and high-speed rotation of the rotating portion 23, for example, high-speed rotation of 5 rotations or more per second becomes easy. In this way, the gantry 5 can be moved at high speed in the body axis (Z-axis) direction by using a high-sensitivity, low-noise detector and increasing the rotation speed of the rotating portion 5 by reducing the weight of the rotating portion 5, so that the number of slices can be increased. The amount of X-ray exposure can be reduced without increasing the amount of X-ray exposure.

FIG. 7C is a circuit configuration diagram for explaining the X generation unit 25 and the light source drive circuit 29 inside the rotating unit 23. The X generation unit 25 is composed of a carbon nanomaterial electron beam generation cold cathode 25C and an anode target 25A. The light source drive circuit 29 is composed of a voltage booster circuit 29-1 and a high voltage control circuit 29-2. Preferably, the light source drive circuit 29 is a transformerless compact, lightweight, low power consumption high voltage power supply unit by using a switching power supply and a power semiconductor. As the secondary battery 27, for example, a lithium ion battery can be used. In this way, the DC voltage of the lithium-ion battery 27 can be boosted by the light source drive circuit 29, and the timing-controlled high-voltage pulse can be applied to the X generation unit 25. The lithium-ion battery 27 is charged by a battery remaining amount detection circuit and a charging circuit (not shown) via the rotating unit interface 2-2 and the host interface 2-1 when the rotating unit 23 is stationary.

FIG. 8A is a plan view of the CT used in the medical vehicle according to the embodiment as viewed from the Z-axis direction for explaining the structure in the gantry. As described above, the fixing portions 24 are combined so as to surround the outer circumference of the rotating portion 23-2. A detector (not shown) is arranged on the inner circumference of the fixed portion 24 over the entire circumference. The rotating unit 23-2 contains an X-ray generating unit 25 m, a light source drive circuit (not shown), a secondary battery, and the like. An opening 28 shown by a broken line is formed in the rotating portion 23-2, and X-rays emitted from the X-ray generating portion can be transmitted or passed through. That is, the influence on the intensity and the traveling direction of the X-ray beam 26 can be reduced. The opening 28 does not necessarily have to have all the members removed (air only), and for example, a protective cover made of resin having high X-ray transmittance, a light-shielding film against visible light, or the like is left. May be. FIG. 8B is a cross-sectional view of the structure inside the gantry when the opening 28 is viewed from the X-axis or Y-axis direction. The detector unit 30 is arranged along the inner circumference of the fixed portion 24, and the X-ray 26 that has passed through the opening 28 reaches the detector unit 30.

FIG. 8C is an enlarged view seen from the Z-axis direction for explaining the structure of the portion related to the broken line portion B in FIG. 8A. Along the annular portion of the fixed portion 24, the plurality of detectors 30 units are continuously and closely arranged so that the longitudinal direction is parallel to the Z axis to form a detector array. That is, FIG. 8 (d) shows a plan view when the opening 28 is viewed from the X-ray generating portion 25 m. Since the pixel arrays of the plurality of detector units 30 attached to the fixed portion 24 are exposed to the X-ray light source 25 m by the opening 28 formed in the rotating portion 23-2, the irradiated X-rays should be shielded. It enables X-ray exposure to the detector unit 30.

With reference to FIG. 9, the detector unit 30 suitable for use in CT in the medical vehicle according to the embodiment, its arrangement, combination, and the like will be described below. In FIG. 9A, a plurality of detector units 30-1 are closely arranged along the inner circumference of the above-mentioned fixed portion 24 so as to surround the rotation center axis 1. As shown in the figure, the detector unit 30-1 includes a vertical shift register 30-12 and a horizontal shift register along two opposing sides in a rectangular light receiving region in which a large number of pixels 30-11 are arranged vertically and horizontally. Peripheral circuits such as the signal readout circuit 30-13 are arranged, and pixels 30-11 are arranged on the remaining two opposite sides even at the end of the light receiving region. The boundary line in which the plurality of detectors 30-1 are in contact is 30-14, and the arrangement pitch of each pixel 30-11 sandwiching this boundary line is inside the light receiving region that does not touch the boundary line 30-14 in the same direction. It is desirable that it is equal to the arrangement pitch of pixels 30-11. For example, this requirement can be satisfied by adopting the structure disclosed in Japanese Patent No. 50273339. As shown in the figure, the plurality of detector units 30-1 have the above-mentioned peripheral circuits formed along two sides where the detector units 30-1 are not adjacent to each other. This is to obtain a continuous pixel signal in the rotation direction of the rotating portion. It is desirable that the element size of the detector unit 30-1 is large, but for example, the so-called medium format size (44 mm x 33 mm) and full size (36 mm x 24 mm), which are widely used in digital cameras and the like. , APS size (23 mm × 15 mm) and other CMOS type image sensor structures and manufacturing methods can be diverted, and the design can be made in accordance with the required specifications of the CT of the present invention.

In FIG. 9B, a plurality of detector units 30-2 are closely arranged along the inner circumference of the above-mentioned fixed portion 24 so as to surround the rotation center axis 1, and are arranged in the direction of the rotation center axis 1. Further, by arranging the detector unit 30-2, the structure in which the number of pixels in the body axis (Z axis) direction is increased is disclosed. As a result, the slice width can be expanded about twice. In this embodiment, the boundary line 30-24 of the detector unit 30-2 that is in close contact with each other on the left and right sides is important in the drawing. This is because it is desirable that the arrangement pitch of each pixel 30-21 having a boundary line sandwiching 30-24 equal to the arrangement pitch of other pixels 30-21 that do not touch the boundary line 30-24 in the same direction. As described above, the structure disclosed in Japanese Patent No. 50273339 is suitable. Further, as shown in the figure, the horizontal and vertical scanning circuits and the signal readout circuits ((30-22, 30-23)) have an arrangement of pixels 30-11 on three sides of the detector unit 30-2 as shown in the figure. In order not to hinder the pitch, the circuit arrangement is concentrated on one side of the detector unit 30-2. In order to further expand the slice width, two or more detectors 30 are arranged on the body axis (Z axis). When arranging in the direction, the above-mentioned horizontal and vertical scanning circuits and signal reading circuits ((30-22, 30-23) hinder the arrangement pitch of the pixels 30-21. An example is disclosed in Japanese Patent No. 5424371.

9 (c) is a cross-sectional view for explaining the structure of the detector 30-2 shown in FIG. 9 (b) in more detail. The detector 30-2 is a CMOS type solid-state image sensor having a back-illuminated structure, and a scintillator layer 46 is laminated on the back surface side. It is sufficient that the thickness of the silicon substrate used in this CMOS type solid-state image sensor is about 5 to 10 microns (μm). This is because the incident X-rays are converted into visible light in the scintillator layer and then read out as an electric signal via the pixel 30-21. Wiring layers 30-27, horizontal and vertical scanning circuits, signal readout circuits ((30-22, 30-23), and connection terminals 30-26) are provided on the front side of the detector unit 30-2. On the back side, shielding members 30-25 for protecting and mitigating integrated circuits from X-ray damage are arranged above horizontal and vertical scanning circuits and signal readout circuits ((30-22, 30-23)). This structure solves the above-mentioned problems that it has been difficult to use a CMOS type detector as a CT X-ray detector unit in the past, and enables low noise, high sensitivity, and high-speed imaging in CT. As a result, the problem of radiation exposure due to X-rays and the like has been alleviated.

An example of CT used in a medical vehicle will be described with reference to FIGS. 10A to 10E. A side view of the CT viewed from the X-axis direction is shown in FIG. 10 (a). As described above, the CT 70 is a CT that takes an image while the sleeper 3-1 moves in the body axis direction while the gantry 5 is stationary. The CT70 is composed of a sleeper 3-1 and a sleeper moving portion (not shown) that supports and moves the sleeper 3-1 and a gantry 5 having an annular cavity portion. Inside the gantry 5, there is a rotatable rotating portion 23, and the rotation center axis 1 is parallel to the Z axis, that is, the body axis direction. A fixing portion 24 is combined around the rotating portion 23 via a ball bearing or the like (not shown). The portion B surrounded by the broken line between the rotating portion 23 and the fixed portion 24 will be described below. It should be noted that there is an operation / control unit and a display (monitor) unit (not shown), and a tomographic image or the like reconstructed by an image drawing circuit, image processing software, or the like is displayed on the monitor.

FIG. 10B is a plan view of the CT70 as viewed from the Z-axis direction. Inside the annular portion of the gantry 5, a rotating portion 23 that rotates around the rotation center shaft 1 is attached via a bearing. Further, a timing belt 21 for rotating the rotating portion 23 and a rotating portion drive motor 19 are attached. A direct drive (DD) motor structure may be formed in which the rotating portion 23 is a rotor and the inner circumference of the gantry 5 surrounding the rotor is a stator. FIG. 10C is an enlarged view of the main part B in FIG. 1A, and a rotating part interface 6-1 made of a metal electrode is formed on the side surface part of the rotating part 23. Since the rotating unit interface 6-1 is located at a position facing the host interface including the convex connection terminal 4, for example, the rotating unit interface 6-1 can be electrically connected by contacting each other when the rotating unit 23 is stationary. It should be noted that preferably, a position sensor or the like (not shown) using a Hall element or the like can be used in order to stop the convex connection terminal 4 and the rotating portion interface 6-1 at a position facing each other. Alternatively, if the rotating portion interface 6-1 is formed in a ring shape over the entire circumference of the annulus on the side surface of the rotating portion 23, electrical connection is possible regardless of the stationary position of the rotating portion 23. Even while the rotating unit 23 is rotating, low-voltage and low-current signals such as control signals and image signals can be transmitted to and received from the fixed unit 24 via the annular rotating unit interface. it can. Alternatively, as described above, the power supply to the light source, for example, the X-ray generating portion or the like is supplied by the secondary battery in the rotating portion, so that it is not necessary to use a slip ring or the like which is a mechanical contact portion. The arrangement of the connection terminal 4 and the rotating unit interface 6-1 is not limited to the case where they come into contact with each other in the Z-axis direction as shown in the drawing, but also in the direction toward 1 toward the central axis (in FIG. 10C, the Y-axis direction). ) May be.

10 (d) and 10 (e) are a cross-sectional view (d) and a plan view (e) seen from the X direction and the Z axis direction for explaining the gantry portion of the CT70 according to the embodiment. FIG. 10D is a cross-sectional view of the rotating portion 23 as viewed from the lateral (X-axis) direction. The X-ray generating unit 25m, which is a component incorporated inside the rotating unit 23, needs to be replaced according to the frequency of use due to deterioration of the target member and wear of the electron beam generating member and the like. Similarly, the detector array 31m may also need to be replaced due to radiation damage to the semiconductor parts used or the humidity dependence of the X-ray scintillator material to be laminated. Therefore, in this embodiment, the X-ray generating portion 25 m and the detector array 31 m of the cartridge structure make it possible to attach / detach from the rotating portion 23 in the Z-axis direction. As shown in the figure, the rotating portion 23 is formed with spaces 25f and 31f (both are broken lines) into which the X-ray generating portion 25m of the cartridge structure and the detector array 31m are inserted. The cartridge structure is not limited to the X-ray generator and the detector array, and the recording capacity of the semiconductor image memory 35 already described may be increased, or the secondary battery 27 may be a cartridge structure. As described above, since the main parts have a cartridge structure, it is easy to deal with a failure even when the medical vehicle is out to a remote place, and the regular maintenance load is remarkably reduced.

FIG. 10E is a plan view of another modification of the CT rotating portion 23 according to the embodiment as viewed from the Z-axis direction. In this embodiment, in addition to the cartridge-structured secondary battery 27 m, the first X-ray generator 25, the second X-ray generator 25-2, and the first position facing each other via the central axis 1 It has a detector array 31 and a second detector array 31-2. The detector array 31 and the detector array 31-2 may be arranged at positions shifted in the Z-axis direction, that is, shifted. Further, the X-ray generating unit 25 and the X-ray generating unit 25-2 may be irradiated with X-rays at the same time or may be irradiated with a time lag. Further, different tube voltages (wavelengths) may be applied to the X-ray generating unit 25 and the X-ray generating unit 25-2 to perform multi-spectral analysis. In this way, despite the miniaturization and weight reduction of the CT main body, imaging under different conditions becomes easy, and more accurate examination, diagnosis, and the like are realized.

A CT suitable for the medical vehicle of the embodiment, particularly a modification relating to the structure of the rotating portion inside the gantry will be described with reference to FIG. 11 (a) is a plan view of the rotating portion 23 inside the gantry 5 as viewed from the Z-axis direction, and FIGS. 11 (b) and 11 (c) are two types of the broken line portion 39 in (a). It is a partially enlarged view for explaining the structure of. As shown in FIG. 11A, the rotating unit 23 includes an X-ray generator 25, a cartridge-structured secondary battery 27 m, a light source drive circuit 29, a cartridge-structured detector array 31 m, and signal amplification / analog digital (AD). ) Detector peripheral circuit 33 including conversion circuit, signal scanning / control circuit, etc., semiconductor image memory 35 m with cartridge structure, detector drive control circuit 41, non-contact interface 12, and digital signal processing circuit (not shown) and parallel serial. It has a built-in conversion circuit, etc. As described below, the regenerative brake circuit 50 is built in the rotating portion 23 or the fixed portion in the gantry, and the electromagnetic induction coil and the permanent magnet are arranged so as to face each other around the rotating portion 23 or the fixed portion. The regenerative braking circuit 50 recovers the electromotive force induced in the electromagnetic induction coil. In the present invention, the term "regenerative braking circuit" is used for convenience, but as will be described later, the rotating portion is positively rotated, not limited to the case where the kinetic energy when the rotating portion decelerates is recovered as electrical energy. This is an effective circuit for converting kinetic energy into electrical energy for continuous power generation.

In the structure (39-1) of FIG. 11B, for example, the north and south poles of the permanent magnets (34-1) are alternately arranged in a ring shape on the fixed portion side. On the other hand, on the rotating portion side, an induction coil (36-1) is wound around an iron core (32-1), and a regenerative braking circuit 50 is provided inside the rotating portion. On the other hand, in the structure (39-2) of FIG. 11C, the north and south poles of the permanent magnets (34-2) are alternately arranged in a ring shape on the rotating portion side. On the other hand, on the fixed portion side, since the induction coil (36-2) is wound around the iron core (32-2), the regenerative brake circuit 50 is provided inside the fixed portion. As will be described later, the structure of FIG. 11B is preferable if electric energy is to be stored in the secondary battery or the electric double layer capacitor inside the rotating portion 23. After the forced rotational motion during imaging is completed, the rotational kinetic energy generated in the induction coil (36-1) can be recovered to the secondary battery in the rotating section or the electric double layer capacitor described later until the rotation is stopped. .. On the other hand, the structure of FIG. 11C is a structure of a DD motor and does not require an external motor and a timing belt. In the structure of FIG. 11B, when the rotating portion 23 is forcibly rotated by an external motor via a timing belt, an electromotive force is generated in the induction coil (36-1), so that the rotating portion 23 rotates twice. It is possible to supply electric power to the light source in the unit, and it has an effect of reducing the addition of the secondary battery 27. As the permanent magnet, for example, a neodymium magnet can be used. When the imaging operation is completed, the rotational movement of the rotating part inside the gantry is unnecessary, but if the moment of inertia of the rotating gantry can be converted into electrical energy without mechanically stopping, an energy saving effect can be obtained. .. In this embodiment, the regenerative brake circuit 50 plays the role. In CT, rotation (imaging mode) and stop (standby mode) are frequently repeated, so the effect of recovering the rotational energy of the rotating part is remarkable, especially when the rotation speed of the rotating part is increased to perform high-speed scanning. The effect is further enhanced.

The regenerative brake 50 will be described below with reference to FIG. 11 (d). The CT having this structure starts the imaging operation after the rotation of the rotating portion 23 starts, and after the imaging is completed, the rotation of the rotating portion 23 is decelerated and the rotational movement is stopped. As described above, since the rotation start and rotation stop are repeated within a short time in one imaging operation, effectively utilizing the rotational kinetic energy of the rotating portion 23 reduces the consumption of the secondary battery and saves energy. Also contributes. FIG. 11D is a circuit configuration diagram for explaining the regenerative brake 50 provided inside the rotating portion 23. One end of the bidirectional DC-DC converter 42 is connected to the secondary battery 27. Further, it is connected to the light source drive circuit 29, the induction coil 36, etc. via the DC-AC converter 48D. On the other hand, the induction coil 36 is connected to the capacitor 44, preferably the electric double layer capacitor, via the AC-DC converter 48A, and further connected to the bidirectional DC-DC converter 42. The rotational kinetic energy of the rotating portion 23 is converted into the counter electromotive force generated in the induction coil 36, and the electric double layer capacitor 44 is charged. Further, the secondary battery 27 can be charged after being converted to a predetermined voltage via the bidirectional DC-DC converter 42. As described above, during CT imaging, when the rotating portion 23 is forcibly rotated by an external motor via a timing belt, an electromotive force is generated in the induction coil (36-1). It can be used to drive the light source drive circuit 29 and the like in the rotating portion. Furthermore, this structure is useful even when CT imaging is stopped other than when CT imaging is performed. That is, the secondary battery built in the rotating portion 23 can be charged by forcibly rotating the rotating portion 23 via the timing belt by an external motor. In this case, since CT imaging is not involved, the rotation speed n2 of the rotating portion during non-CT imaging can be arbitrarily set. Preferably, when the rotation speed of the rotating portion at the time of CT imaging is n1, the rotation speed n2 is increased from the rotation speed n1 (n2> n1) to charge the secondary battery at high speed. That is, as shown in FIG. 11D, power is generated by the induction coil 36, the capacitor 44 is charged via the AC-DC converter 48A, and the secondary battery 27 is further charged via the bidirectional DC-DC converter 42. Can be done. This eliminates the need for power supply via the slip ring, improves the reliability of the CT, reduces the maintenance load, and is particularly suitable as a structure and driving method of the CT used in a medical vehicle.

A driving method when the regenerative brake in the embodiment is used will be described. After the rotation of the rotating portion 23 starts, the movement of the sleeper or the gantry is started. Next, imaging by X-ray irradiation is started. The digital data obtained from the detector array is recorded in the image memory in real time. As described above, the digital data can be recorded in the image memory as the parallel data without the need for parallel serial conversion. After the imaging is completed, the rotational kinetic energy of the rotating portion 23 generates a counter electromotive force in the induction coil and recovers it as electrical energy, and the rotational movement is decelerated while charging the capacitor or the secondary battery. Finally, the gantry stops at a predetermined position, the data recorded in the image memory is read from the rotating unit interface via the host interface, and after the image reconstruction process is performed by the operation / control unit, the shooting information is displayed on the monitor. Will be done. In addition, the secondary battery is charged in parallel, and a series of sequences are completed to enter the standby state.

Generally, the energy recovery efficiency of the capacitor is 90% or more, which is higher than the energy recovery efficiency of about 60% when charging the secondary battery. In particular, it is suitable when the rotating portion 23 decelerates (recovers) and immediately rotates (discharges) the rotating portion 23 as in the present embodiment. The bidirectional DC-DC converter 42 may use a circuit method that combines a step-down chopper circuit and a step-up chopper circuit, or a PWM (Pulse Width Modulation) method that uses a DSP (Digital Signal Processor) and an AD converter. it can. In the case of this configuration, when the secondary battery 27 inside the rotating unit 23 is used as a power source to generate an AC voltage and applied to the electromagnetic induction coil 36-1 to rotate the rotating unit 23, the rotating unit 23 is used as a rotor. , It is also possible to use it as a direct drive (DD) motor in which the fixed portion side of the gantry 5 is a stator.

FIG. 12 shows an example regarding the structure of the rotating portion in the gantry and the driving method, which is suitable for CT used in a medical vehicle. FIG. 12A is a plan view of the gantry 5 viewed from the Z-axis direction, and FIG. 12B is a partially enlarged view for explaining the structure of the broken line portion 39R in FIG. 12A. In this embodiment, the rotating portion 23 is composed of two parts (23-1 and 23-2), one rotating portion (23-1 in this figure) is equipped with a timing belt 21 and the other (23-1). In this figure, 23-2) has a ratchet structure that is mechanically interlocked with the rotating portion (23-1). That is, as shown in FIG. 12B, a movable claw 40 is attached around the rotating portion 23-1, and when the rotating portion 23-1 rotates clockwise, it becomes an inner circumference of the rotating portion 23-2. It can be caught in a groove and transmit torque. On the other hand, when the rotating portion 23-1 stops from deceleration or rotates counterclockwise, the claw 40 slips over the groove on the inner circumference of the rotating portion 23-2 without being able to transmit torque. In addition to the claw seat ratchet structure shown here, an optimum structure such as a ball ratchet structure can be appropriately selected.

FIG. 12 (c) is a flowchart for explaining a method of driving a CT having a gantry using the ratchet structure shown in FIGS. 12 (a) and 12 (b). As shown in the figure, the rotating portion 23-1 starts rotating in the direction in which torque is applied to the rotating portion 23-2, and then or at the same time, the couch or the gantry starts moving. Next, imaging by X-ray irradiation is started. The digital data obtained from the detector array is wirelessly transmitted to the outside in real time or recorded in the image memory built in the rotating unit 23-2. When the rotational torque of the rotating portion 23-1 is reduced or stopped after the imaging is completed, the rotating portion 23-2 is released from the mechanical coupling with the rotating portion 23-1 and idles. Since there is a regenerative braking circuit 50 (not shown) inside the rotating portion 23-2, as already explained with reference to FIG. 11 and the like, a counter electromotive force is generated in the induction coil by the rotational kinetic energy, which is used as electric energy. The rotational movement of the rotating unit 23-2 is decelerated while being collected and charging the capacitor or the secondary battery. Finally, the gantry stops at a predetermined position, the data recorded in the image memory is read from the rotating unit interface via the host interface, and after the image reconstruction process is performed by the operation / control unit (not shown), it is displayed on the monitor. Shooting information is displayed. In addition, the secondary battery is charged in parallel, and a series of sequences are completed to enter the standby state. With this structure, the rotational kinetic energy after the completion of imaging is not converted into the rotational motion of the rotary unit drive motor 19 via the timing belt 21, so that the rotational kinetic energy of the rotary unit 23-2 is efficiently converted into electrical energy by the regenerative brake circuit 50. It becomes possible to collect the energy.

FIG. 13A is a block diagram of a main part for explaining the power supply configuration of the medical vehicle 500 according to the embodiment, particularly centering on the vehicle drive motor 77, CT, and the like. The medical vehicle 500 includes a hydrogen storage tank 75, and uses hydrogen gas to supply the electric energy generated in the fuel cell 73 to the vehicle drive motor 77. Further, it has a vehicle regenerative braking circuit 79 that recovers the regenerative energy associated with the moving vehicle braking of the medical vehicle 500, that is, the deceleration. The main power supply of the CT is supplied from the fuel cell 73 via the gantry 7. Further, while the medical vehicle 500 is moving, the secondary battery inside the gantry 5 can be charged from the vehicle regenerative braking circuit 79 via the gantry 7. In addition, the solar panel 71 makes it possible to use solar energy and charge the lithium ion battery 74 and the like inside the vehicle. The fuel cell 73 _{consumes only hydrogen (H 2} ) and air (Air), and emits only water (H ₂ O). Therefore, there are no problems such as harmful exhaust gas, noise, and vibration, and medical activities such as medical examination can be continued without harming the subject, the medical staff, and the like.

In the above-described embodiment regarding the medical vehicle, the structure in which the part for performing the inspection or medical treatment and the part for driving the vehicle are integrated has been described, but as shown in FIG. 5B, the vehicle for performing the inspection or medical treatment. Needless to say, the 510B may be towed by another movable vehicle 510A. In this case, the vehicle 510B for performing inspection or medical treatment may be of a method of receiving power supply from the driving movable vehicle 510A, or a structure in which a power supply unit such as a fuel cell is built in the vehicle 510B. With this structure, after arriving at the destination, the movable vehicle 510A can separate the vehicle 510B performing the inspection or medical treatment, and tow the vehicle performing another inspection or medical treatment to go to another destination.

The medical vehicle 500 facilitates inspections, medical activities, etc. by going to remote areas, areas affected by earthquakes, typhoons, etc., developing countries, and other places where power supply and refueling cannot be expected. In such an environment, it is often expected that the medical vehicle 500 will be moved into an outdoor tent or inside a building such as an evacuation shelter to continue inspection and medical treatment activities for 24 hours. This is because the energy efficiency of the fuel cell 73 is high, and the spare hydrogen storage tank enables the continuation of medical activities for a long time. Further, as shown in the flowchart of FIG. 13C, the fuel cell 73 mainly supplies electric power to the vehicle drive motor 77 after the medical vehicle 500 starts moving and before using a medical device such as a CT at the destination. However, there is no need to supply electric power to medical devices such as CT. On the other hand, after the medical vehicle 500 is stopped at the destination, the fuel cell 73 mainly supplies electric power to medical equipment such as CT, and it is not necessary to supply electric power to the vehicle drive motor 77. Further, while the medical vehicle 500 is moving, the secondary battery built in the CT can be charged from the vehicle regenerative braking circuit 79.

Mobile hospitals are realized by minimizing the stroke of CT and providing stable power supply means possessed by the vehicle, which also contributes to the realization of so-called "smart cities". By linking with AI (artificial intelligence) and high-speed communication system, it is possible to contribute to the maintenance of people's health from a wide range of perspectives without overlooking various abnormalities that may occur in the human body even in remote areas. By using the medical vehicle of the present invention and combining high-speed communication methods such as 5G and diagnostic imaging using AI, one-stop medical services can be realized even in remote areas and disaster sites, and at the same time, the physical body of medical staff. It is extremely effective in reducing the physical and mental burden, or reducing the risk of infection with viruses and the like.

1: Center of rotation, 2-1: Host interface, 2-2: Rotating part interface, 3: Sleeper, 3-1: Sleeper used in sleeper moving device, 3-2: Sleeper moving device, 3S: Sleeper support part 4: Convex connection terminal, 5: Gantry, 6: Concave connection terminal, 6-1: Rotating part interface, 7: Stand, 9-3, 9-4: Cradle, 10: Non-contact host interface, 11: Gantry Mobile trolley, 12: Non-contact rotating part interface, 13: Gantry moving rail, 14-1, 14-2: Support, 15: Gantry lower wheel, 16-1 to 7: Other space for examination or storage, etc. 16P: In-vehicle passage, 17: Gantry moving carriage drive motor, 18: Stairs or stepping motor, 19: Rotating part drive motor, 20: Subject window, 21: Rotating part rotating belt, 23: Rotating part, 24: Fixed part , 25, 25-2: X-ray generator, 25C: Carbon nanomaterial electron beam generation cold cathode, 25A: Anode target, 26: X-ray beam, 27: Secondary battery, 28: Opening, 29: Light source drive circuit , 29-1: Voltage booster circuit, 29-2: High voltage control circuit, 30: Detector unit, 31, 31-2: Detector array, 32-1, 32-2: Iron core, 33: Around the detector Circuit, 34-1, 34-2: Permanent magnet, 35: Image memory, 36: Induction coil, 37: Gantry storage part, 38: Bus line, 39: Outer circumference of rotating part 5 and part of outer circumference of gantry part 23, 39R: Ratchet structure, 40: Ratchet mechanism claw part, 41: Detector drive control circuit, 42: Bidirectional DC-DC converter, 43: Signal amplification / AD conversion circuit, 44: Electric double layer capacitor, 45: Signal scanning Control circuit, 46: scintillator, 47: digital signal processing circuit, 48A: AC-DC converter, 48D: DC-AC converter, 49: parallel serial conversion circuit, 50: rotating part regenerative braking circuit, 51, 51-2: Subject protection member, 52: sliding door, 52-1, 52-2: openable door, 52-3: back door, 53: funnel-shaped subject protection member, 55-1: vehicle body floor surface, 55-3: vehicle body side surface , 57: Space before and after CT, 59: Auxiliary plate, 61, 63, 65, 67-1, 67-2, 69-1, 69-2: CT mounted on the vehicle, 62: Stretcher, 71: Solar Panel, 73: Fuel cell, 74: Lithium ion battery in the vehicle, 75: Hydrogen storage tank, 77: Vehicle drive motor, 79: Vehicle regenerative brake

The medical vehicle 200 according to the embodiment and the medical vehicle 210 according to the modified example will be described below with reference to FIGS. 2 (a) and 2 (c). FIG. 2A is a side view of the medical vehicle 200 according to the embodiment as viewed from the Z-axis direction. However, unlike the case of FIG. 1A, the front of the medical vehicle 200 is to the right in the drawing. On the side surface of the vehicle, there is a subject window 20 for inserting a sleeper (3-1) on which a subject such as a human body is placed along the upper part of the sleeper holding plate 3S inside the CT63. In CT63, the body axis direction of the gantry coincides with the Z axis direction. In this embodiment, a case where imaging is performed while moving the bed (3-1) on which the subject is placed with the gantry portion fixed will be described. FIG. 2B is a plan view of a main part of the medical vehicle 200 as viewed from the Y-axis direction. In this embodiment, the subject window portions 20 are provided on the left and right side surfaces of the medical vehicle 200, and a funnel-shaped subject protection member 53 is attached between the subject insertion portion and the subject window portion 20 of the CT63. and which, outside air outside the vehicle as will be described later is prevented from entering the interior of the medical vehicle 200. From one side of the vehicle of the medical vehicle 200, the subject is guided into the CT63 by the transport unit 3-2 of the sleeper moving device in a state of lying on the bed 3-1 of the sleeper moving device. That is, the stroke region required by the CT 63 is not inside the medical vehicle 200, but outside the medical vehicle 200. In this embodiment, the gantry 5 is fixed to the substantially central portion of the medical vehicle 200 in the Z-axis direction. Inside the gantry 5, there is a rotatable rotating unit, and an operation / control unit and a display (monitor) unit (not shown) are provided in the vehicle. That is, a tomographic image or the like reconstructed by an image drawing circuit, software, or the like is displayed on the monitor. Further, in the medical vehicle 200, similarly to the medical vehicle 100, spaces (16-1 to 16-6, and 16P) for other purposes, stairs 18, and the like are arranged. Further, when the CT63 is not used, for example, while the medical vehicle 200 is running, the doors 52-1 and 52-2 that can be opened and closed are provided to shut the CT63 from the outside of the vehicle. With this structure, the subject can be carried in or out from either the left or right side of the medical vehicle 200.

Claims (17)

A medical vehicle having a CT, the CT having a light source that rotates around a subject about a body axis direction, the body axis direction being orthogonal to the straight-ahead direction of the medical vehicle in the horizontal direction, and A medical vehicle having a window portion on the left side surface or the right side surface of the medical vehicle for introducing or carrying out the subject or a sleeper on which the subject is placed on the inner circumference of the CT gantry. A medical vehicle having a CT, wherein the CT has a light source that rotates around a subject about a body axis direction, the body axis direction coincides with the straight-ahead direction of the medical vehicle in the horizontal direction, and the body axis direction is the same. A medical vehicle having a window portion on the rear side surface of the medical vehicle for introducing or carrying out the subject or a sleeper on which the subject is placed on the inner circumference of the CT gantry. The medical vehicle according to claim 1 or 2, wherein the gantry is attached in the vicinity of the window portion. The claim that the shape of the window portion viewed from the body axis direction is circular, and the diameter of the circular window portion is a funnel shape larger than the diameter of the inner peripheral portion of the gantry viewed from the body axis direction. 1 or the medical vehicle according to claim 2. The medical vehicle according to claim 1 or 2, further comprising a tubular subject protection portion penetrating the inner peripheral portion of the gantry. The subject protection portion is continuously formed from the window portion, and the end portion of the subject protection portion at a position facing the window portion has a closed shape that blocks outside air from the inside of the medical vehicle. The medical vehicle according to claim 5. The medical vehicle according to claim 1, wherein the subject protection unit is formed continuously from the window portion on the left side surface to the window portion on the right side surface, which is cited in claim 5. The medical vehicle according to claim 5, wherein the opening area of the window portion is larger than the opening area of the subject protection portion, and the medical vehicle has a space portion having a depth toward the inside of the medical vehicle. A light source, a light source drive control circuit, a detector at a position facing the light source with the rotation center axis of the rotating portion sandwiched in a rotating portion inside the gantry, the detector is driven, and an output signal of the detector is processed. The medical vehicle according to claim 1 or 2, wherein a detector control signal processing circuit and a secondary battery for driving these circuits are incorporated. A light source, a light source drive control circuit, and a secondary battery for driving these are built in the rotating portion inside the gantry, and the entire inner circumference of the annular fixed portion concentric with the rotating portion is surrounded by the rotating portion. A plurality of detectors are mounted on the circumference, and the portion facing the light source with the rotation center axis of the rotating portion sandwiched therein, and the light emitted from the light source is passed through to pass the light receiving surface of the detector. The medical vehicle according to claim 1 or 2, wherein the rotating portion has an opening to be exposed. A plurality of induction coils are arranged along the outer peripheral portion of the rotating portion inside the gantry, and the north and south poles are alternately arranged along the inner circumference of the circumferential portion of the gantry surrounding the rotating portion. The medical vehicle according to claim 1 or 2, further comprising a regenerative braking circuit in which a permanent magnet is arranged on the vehicle and the rotational kinetic energy of the rotating portion is converted into electrical energy by the induction coil. 15. Described medical vehicle. The medical vehicle according to claim 1 or 2, wherein the light source is an X-ray light source, and the electron beam generating portion of the X-ray light source is composed of carbon nanostructures. The medical vehicle according to claim 9, wherein any of the secondary battery, the light source, and the detector in the rotating portion has a cartridge structure. The medical vehicle according to claim 1 or 2, wherein the power source for driving the CT is a fuel cell using hydrogen as a raw material. The medical vehicle according to claim 15, wherein the fuel cell is a power source for electrically driving the medical vehicle. The medical vehicle according to claim 9 or 10, wherein the vehicle regenerative braking circuit for converting the kinetic energy at the time of deceleration of the medical vehicle into electric energy and charging the secondary battery is connected to the secondary battery. ..

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