WO2015186651A1

WO2015186651A1 - Ultrasound therapeutic device and ultrasound therapeutic system

Info

Publication number: WO2015186651A1
Application number: PCT/JP2015/065732
Authority: WO
Inventors: 仲本　秀和
Original assignee: 株式会社日立メディコ
Priority date: 2014-06-05
Filing date: 2015-06-01
Publication date: 2015-12-10
Also published as: JPWO2015186651A1; JP6473149B2

Abstract

An ultrasound therapeutic device has a therapeutic probe (37a). The therapeutic probe (37a) is divided into multiple groups of channels (G1-G4). Each group of channels (G1-G4) has multiple therapeutic oscillators (39). The oscillators (39) belonging to a certain group of channels (G1) first emit a trigger ultrasonic wave (801) toward a focal point (403) in the body of a patient (24). The trigger ultrasonic wave (801) is in the form of pulses and the amplitude (a1) thereof is large. The trigger ultrasonic wave (801) produces bubbles at the focal point (403). The oscillators (39) belonging to the remaining groups of channels (G2-G4) next emit a heating ultrasonic wave (802) toward the focal point (403). The heating ultrasonic wave (802) is a continuous wave and the amplitude (a2) thereof is small. The heating ultrasonic wave (802) destroys the bubbles produced by the trigger ultrasonic wave (801). The heat generated accompanying said destruction induces coagulation of the tissue. The trigger ultrasonic wave (801) and the heating ultrasonic wave (802) reach the same focal point (403) through different parts of the skin. Burns to the skin are thereby avoided.

Description

Ultrasonic therapy apparatus and ultrasonic therapy system

The present invention relates to an ultrasonic therapy apparatus and an ultrasonic therapy system, and relates to an ultrasonic therapy apparatus for irradiating a target site set in a living body with high-intensity focused ultrasound (HIFU: High Intensity Focused Ultra sound), and The present invention relates to an ultrasonic therapy system.

In HIFU treatment, an embolus with a high blood flow blocking effect is achieved by irradiating the focus set on the treatment site with high-density focused ultrasound to locally heat the lesion and thermally coagulating the tissue in the lesion. It is known as a less invasive treatment for realizing the treatment. For example, it has been proposed to insert a treatment probe into the rectum of a living body and irradiate HIFU to the lesioned part at the site to be treated.

In addition, the ultrasonic treatment apparatus using HIFU introduced in Patent Document 1 is an ultrasonic electrical signal (hereinafter referred to as an ultrasonic signal) supplied from a multi-channel generator, and a plurality of treatment transducers (transducers). ) Have been proposed. According to this, by controlling the amplitude, frequency, and phase of the ultrasonic wave emitted from each treatment vibrator independently, it is possible to treat a wide range of treatment target parts by moving the focal position.

Generally, in HIFU treatment, a pulsed trigger ultrasonic wave with high ultrasonic intensity is irradiated, and then a continuous ultrasonic wave (CW) heating ultrasonic wave with a lower intensity than the trigger ultrasonic wave is irradiated for a predetermined time. By repeating, treatment is performed by irradiating a treatment target site with predetermined therapeutic ultrasonic energy.

Japanese Patent No. 4519905 JP 2011-115461 A

However, Patent Document 1 does not consider avoiding the risk of burns occurring on the surface of the living body (skin) on the irradiation path of HIFU.

That is, in Patent Document 1, a trigger ultrasonic wave is irradiated from all of a plurality of treatment vibrators constituting a multichannel toward a focal point, and then a heating ultrasonic wave is irradiated. Usually, HIFU is irradiated between a treatment probe and a living body surface with, for example, a water bag filled with deaerated water interposed therebetween. In this case, since the acoustic impedances of water and the surface of the living body (skin) are extremely different, the trigger ultrasonic waves are reflected at the boundary between the water and the surface of the living body to accumulate ultrasonic energy, and bubbles are generated due to the cavitation phenomenon. When heated ultrasonic waves are applied subsequent to the bubbles, the bubbles are destroyed, and the skin may be burned by the heat of destruction. When skin burns occur, not only is the propagation of the treatment ultrasound inhibited and the treatment ultrasound site is not irradiated with the treatment ultrasound, but also damage to normal tissue becomes a problem.

The problem to be solved by the present invention is to provide an ultrasonic treatment apparatus and an ultrasonic treatment system that can effectively avoid the risk of skin burns.

In order to solve the above-described problems, an ultrasonic treatment apparatus and an ultrasonic treatment system according to the present invention include a treatment probe having a plurality of channels including treatment transducers that generate treatment ultrasonic waves, and a living body from the treatment probe. A treatment probe control unit that repeats a treatment ultrasonic cycle that irradiates a heating ultrasonic wave having a lower intensity than the trigger ultrasonic wave at a focal point set in a treatment target region, and the treatment probe control unit includes: The divided irradiation is performed so that the channel that irradiates the trigger ultrasonic wave toward the focal point and the channel that irradiates the heated ultrasonic wave toward the focal point are different for each treatment ultrasonic cycle. And

That is, the present invention divides a plurality of channels into a channel for irradiating a trigger ultrasonic wave and a channel for irradiating a heating ultrasonic wave, and switching the channel for irradiating the trigger ultrasonic wave every time the treatment ultrasonic cycle is repeated. Features. In other words, when trigger ultrasonic waves are irradiated from one channel and subsequently heated ultrasonic waves are irradiated from the same channel, bubbles generated by the trigger ultrasonic waves are destroyed by the heated ultrasonic waves, and the heat of bubble destruction is generated. In view of the above, the present invention is characterized in that the channels for transmitting the trigger ultrasonic wave and the heating ultrasonic wave are different. In other words, the propagation path (ultrasonic beam) of the trigger ultrasonic wave in the vicinity of the body surface and the propagation path (ultrasonic beam) of the heating ultrasonic wave are made different for each treatment ultrasonic cycle.

As in the present invention, even if the channels for transmitting the trigger ultrasonic wave and the heating ultrasonic wave are different, the ultrasonic beam of each channel is focused on the focal point set in the treatment target region. The bubbles generated at the focal point by the trigger ultrasonic wave are irradiated with heating ultrasonic waves from different propagation paths, and the bubbles are destroyed, so that the tissue at the focal point can be thermally coagulated to perform ultrasonic treatment. .

According to the present invention, skin burns can be effectively avoided.

The figure which shows the whole structure of the ultrasonic treatment system of one Embodiment of this invention. The block block diagram of the ultrasonic therapy apparatus of one Embodiment of this invention The figure explaining the structure of the ultrasonic probe of one Embodiment of this invention The figure which shows arrangement | positioning of the treatment ultrasonic beam and the some treatment vibrator | oscillator (channel) transmitted from the some treatment vibrator | oscillator of the treatment probe of one Embodiment of this invention. Diagram illustrating treatment ultrasound cycle Illustration explaining HIFU treatment The figure explaining the navigation guide display function of the ultrasonic treatment system of one embodiment of the present invention The flowchart which shows the treatment procedure of the ultrasonic treatment system of one Embodiment of this invention. FIG. 8 is a detailed flowchart of a portion related to the characteristic part of the embodiment of the present invention shown in the flowchart of FIG. The figure explaining division | segmentation of the channel group which divides and irradiates a trigger ultrasonic wave and a heating ultrasonic wave according to the distance from a focus to a body surface The figure explaining the method of calculating | requiring the compensation value of the treatment ultrasonic energy of the channel unit which divides and irradiates a trigger ultrasonic wave and a heating ultrasonic wave, and the channel unit which concerns on a division | segmentation irradiation The figure explaining Example 1 which divides and emits the trigger ultrasonic wave and the heating ultrasonic wave which are the characteristics of this invention The figure explaining Example 2 which divides and irradiates the trigger ultrasonic wave and heating ultrasonic wave which are the characteristics of this invention The figure explaining Example 3 which divides and irradiates the trigger ultrasonic wave and heating ultrasonic wave which are the characteristics of this invention FIG. 6 is a diagram for explaining a fourth embodiment in which the trigger ultrasonic wave and the heating ultrasonic wave are separately irradiated, which is a feature of the present invention FIG. 6 is a diagram for explaining a fifth embodiment in which the trigger ultrasonic wave and the heating ultrasonic wave are separately irradiated, which is a feature of the present invention FIG. 6 is a diagram for explaining a sixth embodiment in which the trigger ultrasonic wave and the heating ultrasonic wave are separately irradiated, which is a feature of the present invention. FIG. 6 is a diagram for explaining a seventh embodiment in which the trigger ultrasonic wave and the heating ultrasonic wave are separately irradiated, which is a feature of the present invention. The figure which shows an example of the display of the graphic user interface (GUI) of the ultrasonic treatment system of this invention

The ultrasonic therapy apparatus according to the present invention includes a treatment probe having a plurality of channels including treatment transducers for generating a treatment ultrasonic wave, and a trigger ultrasound at a focus set from the treatment probe to a treatment target site of a living body. A therapeutic probe control unit that repeats a therapeutic ultrasonic cycle that irradiates a heating ultrasonic wave having a lower intensity than the trigger ultrasonic wave following the acoustic wave, and the therapeutic probe control unit performs the trigger ultrasonic cycle for each therapeutic ultrasonic cycle. The divided irradiation is performed such that the channel that irradiates the sound wave toward the focal point and the channel that irradiates the heating ultrasonic wave toward the focal point are different.

The treatment probe control unit compensates for the ultrasonic energy of the trigger ultrasonic wave and the heating ultrasonic wave constituting the therapeutic ultrasonic cycle according to a target value of the therapeutic ultrasonic energy irradiated toward the focal point. It is characterized by doing.

Further, the target value of the therapeutic ultrasonic energy is basic therapeutic ultrasonic energy that irradiates the heating ultrasonic wave toward the focal point following the trigger ultrasonic wave from each channel.

Further, the treatment probe control unit measures the distance from the focal point to the body surface of the living body, and performs the divided irradiation when the measurement distance is within a predetermined minimum value and maximum value range, When the measurement distance exceeds the maximum value, instead of the divided irradiation, basic irradiation is performed by irradiating the heating ultrasonic wave toward the focal point following the trigger ultrasonic wave from all the channels. And

In addition, a monitor that displays an arrangement configuration image of the plurality of channels of the treatment probe is provided, and the monitor irradiates the trigger ultrasonic wave toward the focal point and the heating ultrasonic wave toward the focal point. The irradiation channel is displayed in a different display form.

Further, the treatment probe is formed by dividing the hemispherical concave surface into a plurality of concentric annular regions, and further forming the channel in each of a plurality of regions obtained by dividing the annular region in the radial direction, The area of the ultrasonic wave transmission surface of each channel is formed uniformly.

In addition, the treatment probe control unit divides the plurality of channels into a channel group including a plurality of channels, irradiates the trigger ultrasonic wave from the channels belonging to one channel group toward the focal point, and then the other channels. A treatment ultrasonic cycle for irradiating the heating ultrasonic wave from the channels belonging to the channel group toward the focal point is repeated, and one channel group for irradiating the trigger ultrasonic wave for each repetition of the treatment ultrasonic cycle is changed to another channel group. Switching to one of the channel groups.

In addition, the treatment probe control unit adjusts at least one of the amplitude, frequency, or irradiation time of the trigger ultrasonic wave or the amplitude of the heating ultrasonic wave in accordance with a target value of the therapeutic ultrasonic energy irradiated toward the focal point. The ultrasonic energy is compensated by adjusting at least one of the frequency and the irradiation time.

The target value of the therapeutic ultrasonic energy is a reference therapeutic ultrasonic energy that irradiates the heating ultrasonic wave toward the focal point following the trigger ultrasonic wave from each channel.

Further, when the number of the plurality of channels is n and the number of the plurality of channels of the channel group is m, the treatment probe control unit multiplies the amplitude of the trigger ultrasonic wave by n / m, or The therapeutic ultrasonic energy is compensated by adjusting the trigger ultrasonic energy by multiplying the frequency of the trigger ultrasonic wave by an integer.

In addition, when the treatment probe energy compensation compensates the treatment ultrasound energy, if the energy of the trigger ultrasound or the energy of the heating ultrasound exceeds a preset upper limit value, a warning to that effect is given by sound or sound. Or it alert | reports by image information, It is characterized by the above-mentioned.

In addition, the upper limit value is set to a value that prevents burns on the body surface of the living body located between the channel and the focal point.

In addition, the ultrasonic treatment system according to the present invention includes a treatment probe having a plurality of channels including treatment transducers that generate treatment ultrasonic waves, and a focal point set from the treatment probe to a treatment target site of a living body. A treatment probe controller that repeats a treatment ultrasound cycle that irradiates a heating ultrasound that is less intense than the trigger ultrasound following the trigger ultrasound, and is provided at the center of the treatment probe for imaging with the living body An imaging probe having a plurality of imaging transducers for transmitting and receiving the ultrasound, an ultrasound image forming unit for generating an ultrasound image including the focal point generated from a reception signal of the imaging probe, and the ultrasound A display unit for displaying an image, and the treatment probe control unit irradiates the trigger ultrasonic wave toward the focal point for each treatment ultrasonic cycle. When, and performing fractionated irradiation made different and the channel for irradiating the heating ultrasound to the focal point.

A three-dimensional position detector for detecting the position of the treatment probe; a memory in which three-dimensional volume image data including the treatment target portion of the living body is stored; and the three-dimensional position detector A medical image device having a navigation image configuration unit that generates a navigation image corresponding to a tomographic plane of the ultrasonic image from the three-dimensional volume image data based on the position of the treatment probe and displays the navigation image on the display unit; The medical imaging apparatus includes a therapeutic ultrasound beam rendering unit that generates a simulated image of a therapeutic ultrasound beam that connects each channel and the focal point and overlays the navigation image, and the treatment probe control unit includes: Based on the ultrasonic image displayed on the display unit, the distance from the focal point to the body surface of the living body is measured, and the measurement distance Is performed within the range between a predetermined minimum value and a maximum value, and when the measurement distance exceeds the maximum value, the trigger is exceeded from all the channels instead of the divided irradiation. A basic irradiation is performed in which the heating ultrasonic wave is irradiated toward the focal point following the sound wave.

Hereinafter, the present invention will be described in detail based on embodiments with reference to the drawings.

FIG. 1 shows the overall configuration of the ultrasonic therapy system of the present invention. A magnetic resonance imaging (MRI) apparatus 1 which is one of medical imaging apparatuses is, for example, a perpendicular magnetic field permanent magnet type MRI apparatus. However, the present invention is not limited to the vertical magnetic field permanent magnet type MRI apparatus, and other types of known medical image apparatuses such as an MRI apparatus, a CT apparatus, a PET apparatus, and an ultrasonic image apparatus can be applied.

As shown in the figure, the MRI apparatus 1 of the present embodiment includes an upper magnet 3 and a lower magnet 5 that generate a vertical static magnetic field, a support 7 that connects these magnets and supports the upper magnet 3, a position detection device 9, and an arm. 11, monitors 13 and 14, a monitor support unit 15, a reference tool 17, a personal computer 19, a bed 21, an MRI control unit 23, and the like. A gradient magnetic field generator (not shown) of the MRI apparatus 1 generates a gradient magnetic field. Further, the MRI apparatus 1 includes an RF transmitter (not shown) for generating nuclear magnetic resonance in the patient 24 in a static magnetic field and an RF receiver (not shown) for receiving a nuclear magnetic resonance signal from the patient 24.

The position detection device 9 is a three-dimensional position detector that detects the three-dimensional position and posture of the ultrasonic probe 37 (hereinafter collectively referred to as a position). That is, the position detection device 9 includes two infrared cameras 25 and a light emitting diode (not shown) that emits infrared light, and detects the three-dimensional position of the pointer 27 attached to the ultrasonic probe 37. Thus, the pointer 27 functions as an instruction device for an imaging tomographic plane of the ultrasonic image and the MR image, together with a function of detecting the position and inclination of the ultrasonic probe 37 (hereinafter collectively referred to as a position).

Further, the position detection device 9 is connected to the upper magnet 3 so as to be movable by the arm 11, and is formed so that the arrangement with respect to the MRI apparatus 1 can be appropriately changed. On the monitor 13, an ultrasonic image of the tomographic plane of the patient 24 indicated by the pointer 27 held by the operator 29 is displayed. The monitor 13 is connected to the upper magnet 3 by the monitor support portion 15 in the same manner as the infrared camera 25. The reference tool 17 links the coordinate system of the infrared camera 25 and the coordinate system of the MRI apparatus 1, includes three reflection spheres 35, and is provided on the side surface of the upper magnet 3.

The position information of the pointer 27 detected and calculated by the infrared camera 25 is transmitted to the personal computer 19 as position data of the ultrasonic probe 37, for example, via the RS232C cable 33. The MRI control unit 23 is composed of a workstation and controls an RF transmitter, an RF receiver, etc. (not shown). Further, the MRI control unit 23 is connected to the personal computer 19. In the personal computer 19, the position data of the pointer 27 detected and calculated by the infrared camera 25 is converted into position data of the imaging range in the MRI apparatus 1 and transmitted to the MRI control unit 23. The position data is reflected in the control of the imaging section of the imaging sequence. The MR image acquired with the new imaging section is displayed on the monitor 13. MR images are simultaneously recorded in the video recording device 34.

The ultrasonic therapy apparatus 40 displays an ultrasonic image obtained by the ultrasonic probe 37 to which the pointer 27 is attached on a dedicated monitor 38. The ultrasonic image is transferred to the personal computer 19 for image processing and displayed on the operator monitors 13 and 14. The ultrasonic probe 37 is formed of a non-magnetic material such as ceramic that can be operated even in the magnetic field of the MRI apparatus 1. Further, as will be described with reference to FIG. 3, the ultrasound probe 37 includes a treatment probe 37a for irradiating HIFU treatment ultrasound and an imaging probe 37b for imaging ultrasound images.

The ultrasonic therapy apparatus 40 includes a HIFU controller 49 formed by a computer such as a personal computer, and a power amplifier 50 that amplifies the HIFU ultrasonic signal output from the HIFU controller 49. The ultrasonic signal output from the power amplifier 50 is supplied to the treatment probe 37a of the ultrasonic probe 37. As a result, HIFU treatment is performed by irradiating the patient 24 with HIFU (high density focused ultrasound) from the treatment probe 37a.

FIG. 2 shows a block configuration of the main part of the ultrasonic therapy apparatus 40. The ultrasonic therapy device 40 includes an ultrasonic transmission / reception unit 44 that transmits and receives an ultrasonic signal to and from the imaging probe 37b, and a two-dimensional ultrasonic image (for example, a B-mode image) including a HIFU focus based on the received signal. An ultrasonic image composing unit 45 that constitutes a sound image, a monitor 38 that is a display unit that displays an ultrasonic image composed of the ultrasonic image composing unit 45, an ultrasonic control unit 47 that controls each component, The control panel 48 is configured to give instructions to the sound wave control unit 47.

The ultrasound image constructing unit 45 uses a reflected echo signal obtained by transmitting and receiving ultrasound from the imaging probe 37b to the patient 24 by the ultrasound transmitting / receiving unit 44, and a two-dimensional ultrasound image or a three-dimensional image including a treatment target region. An ultrasonic image is formed and displayed on the monitor 38.

The HIFU controller 49 drives the imaging probe 37b via the ultrasound control unit 47 to irradiate the patient 24 with weak ultrasound for imaging when the ultrasound therapy apparatus 40 is operated as an ultrasound imaging apparatus. That is, the ultrasound control unit 47 weakens the energy of the ultrasound irradiated to the patient 24 when operating the ultrasound therapy apparatus 40 as a diagnostic apparatus. On the other hand, when the ultrasonic therapy apparatus 40 is operated as a therapy apparatus, the ultrasonic control unit 47, via the HIFU controller 49, increases the intensity of the ultrasonic wave to be irradiated so as to increase the energy of the ultrasonic wave irradiated to the patient 24. To control.

That is, the HIFU controller 49 constitutes the treatment probe control unit of the present invention, and outputs an HIFU ultrasonic signal to the power amplifier 50 based on a command output from the ultrasonic control unit 47. The power amplifier 50 amplifies the ultrasonic signal of HIFU and outputs it to the treatment probe 37a. Thereby, a strong ultrasonic wave for treatment is irradiated to a predetermined part of the patient 24 from the treatment probe 37a. In other words, the HIFU controller 49 and the power amplifier 50 determine the intensity (energy) of the therapeutic ultrasound beam emitted from the treatment probe 37a including a plurality of treatment transducers 39 that constitute a channel for emitting treatment ultrasound of the treatment probe 37a. Each is to be controlled. Note that the ultrasonic frequency emitted from the treatment probe 37a can be selectively used as 2 MHz or 1 MHz as necessary, and is controlled by the HIFU controller 49.

In addition, the HIFU controller 49 is linked to the ultrasonic therapy apparatus 40 so that the state transition of the treatment target site before and after the HIFU irradiation can be understood. Before the HIFU irradiation, it also has a function of performing image processing for rendering the skin, which is the body surface of the patient 24, using a diagnostic image inside the ultrasonic therapy apparatus 40. Information generated by the ultrasonic therapy apparatus 40 can be shared with the HIFU controller 49.

In the example of FIGS. 1 and 2, the ultrasonic diagnostic apparatus 40 is configured to incorporate the ultrasonic diagnostic apparatus, but the ultrasonic diagnostic apparatus and the ultrasonic therapeutic apparatus may be configured as separate apparatuses. Further, although the ultrasonic therapy device 40 and the HIFU controller 49 are separate devices, they may be configured as an integrated device.

3 and 4 are configuration diagrams of an embodiment of the ultrasonic probe 37 according to the feature of the present invention. 3A is a cross-sectional view of a plane passing through the central axis of the ultrasonic probe 37, and FIG. 3B is a front view of the ultrasonic probe 37 viewed from the ultrasonic transmission surface side. As is clear from the figure, the ultrasonic probe 37 is formed by including a treatment probe 37a formed on a concave spherical surface and an imaging probe 37b for imaging an ultrasonic image disposed on the central axis of the concave spherical surface. ing. The imaging probe 37b is an imaging ultrasonic probe for imaging and drawing a tomographic image (ultrasonic image) of the fan-shaped region 601 including the focal point of the treatment target region.

The treatment probe 37a can be formed by arranging channels C composed of a plurality of treatment transducers 39 on a two-dimensional plane or a three-dimensional curved surface. However, as shown in FIG. 4 (b), the treatment probe 37a of the present embodiment divides the concave spherical surface into a plurality of concentric annular regions, and further includes a plurality of annular regions divided in the radial direction. Each region is formed with a treatment transducer 39 disposed therein. Each therapeutic transducer 39 forms a channel C of a therapeutic ultrasonic beam.

In other words, the treatment probe 37a is formed of a multichannel including a plurality of treatment transducers 39 that send out a treatment ultrasonic beam. Here, the number of treatment transducers 39 is 40 in the illustrated example for simplification, but the number of treatment transducers 39 is generally a power of 2, for example, 512 And 1024 are used. The imaging probe 37b is an imaging ultrasonic probe for imaging and drawing the tomographic plane 601 including the focus of the treatment target region.

In FIG. 4 (b), the plurality of divided treatment transducers 39 will be described as treatment ultrasound irradiation channels (hereinafter simply referred to as channels). As shown in the figure, the concave spherical surface is divided into a plurality of concentric annular regions i (i = 5 in the illustrated example), and the annular region is further divided into a plurality of regions j in the radial direction (in the illustrated example, j = 8), a plurality of n (n = 1, 2,..., Arbitrary natural numbers) channels Cij are provided. The therapeutic ultrasound beam 404a emitted from each channel Cij is focused on the focal point 403. In other words, by independently controlling the phase of the therapeutic ultrasonic wave transmitted from each channel Cij, the transmission angle of the plurality of therapeutic ultrasonic beams 404a can be controlled and focused on the focal point 403. In addition, the focus 403 can be moved in three dimensions (front and rear, left and right, depth direction) by phase control of therapeutic ultrasound.

Fig. 5 shows the basic pattern of HIFU irradiated from the therapeutic probe 37a. As shown in the figure, the HIFU repeatedly irradiates a treatment ultrasonic cycle that irradiates a heated ultrasonic wave 802 having a lower intensity than the trigger ultrasonic wave 801 following a trigger ultrasonic wave 801 having a high ultrasonic intensity. In other words, by repeating the treatment ultrasonic cycle of irradiating the trigger ultrasonic wave 801 with the set trigger time t1 and the heated ultrasonic wave 802 with the set heating time t2, the focus 403 is irradiated with HIFU for a total set time T for treatment. Do.

Here, conventionally, each channel Cij is basically driven by the same therapeutic ultrasonic cycle to perform the treatment. The trigger ultrasonic wave 801 is an instantaneous high-intensity pulse for generating bubbles, and the heating ultrasonic wave 802 is composed of a continuous wave (CW) that destroys the generated bubbles and induces thermal coagulation. Yes. For example, the trigger ultrasonic wave 801 having the amplitude a1 is irradiated with the trigger time t1 (for example, several μsec), and then the heating ultrasonic wave 802 having the amplitude a2 is irradiated with the heating time t2.

This therapeutic ultrasound cycle is defined by the number of repetitions per second: Pulse Repetition Frequency (PRF) and the total set time T, which defines the HIFU intensity. That is, by controlling the amplitude and frequency of the trigger ultrasonic wave 801 and the heating ultrasonic wave 802 and their irradiation time, the HIFU intensity or the intensity of the therapeutic ultrasonic beam 404a (the therapeutic ultrasonic energy) can be controlled.

For example, if the trigger time t1 is set long and the PRF is set small, bubbles are easily generated. However, there is a high possibility that energy concentrates on the skin through which the HIFU beam 404a passes to cause burns. However, there is a conflicting feature that the ablation range at the focal point 403 of the treatment target region becomes large and the treatment effect can be improved. That is, when the trigger ultrasonic wave is irradiated for PRF times x trigger time t1 per second, the cavitation occurrence rate is improved in proportion to the irradiation time of the trigger ultrasonic wave 801. Concerns about skin burns due to the heat of bubble destruction increase. Patent Document 2 introduces the content of transmitting a pulse for generating bubbles and a pulse for increasing the diameter of the generated bubbles to a target region of a living body. As a result, it is possible to realize an embolization treatment that is minimally invasive and has a high blood flow blocking effect.

Next, an outline of performing treatment by irradiating with high-intensity focused ultrasound (HIFU) will be described with reference to FIG. As shown in FIG. 6 (a), the HIFU beam 404, which is a bundle of therapeutic ultrasound beams 404a transmitted from each treatment transducer 39 of the treatment probe 37a, is focused on a focal point 403 and irradiated.

In addition, as shown in FIG. 6 (b), the range of treatment (cauterization) by irradiating one focal point 403 with HIFU is, for example, a diameter Φ of 5 to 10 mm. Therefore, when performing treatment with HIFU irradiation, the position of the focal point 403, which is the irradiation position of the HIFU beam 404, is sequentially moved as shown in FIG. Irradiate the beam 404. At that time, the state of treatment is monitored by an ultrasonic image captured by the imaging probe 37b attached to the center of the ultrasonic probe 37.

However, if treatment and monitoring are performed simultaneously, they will appear in the image as noise. Therefore, a clear diagnostic image free from noise is acquired by operating the treatment probe 37a and the imaging probe 37b alternately. In addition, by performing focus visualization with ARFI (Acoustic Radiation Force Impulse) as shown in Non-Patent Document 1, the actual affected area in the living tissue is calculated for the ideal ablation area, and three-dimensional measurement is performed. Thus, a three-dimensional treatment planned area can be calculated.

Next, the navigation guide display function of this embodiment will be described with reference to FIG. The surgeon 29 adjusts the focus 403 of the treatment probe 37a connected to the HIFU controller 49 via the power amplifier 50 with respect to the patient 24 to one point of the treatment target site (target).

That is, the position of the ultrasonic probe 37 is detected from the position of the pointer 27 with an infrared camera attached to the position detection device 9, and simulated images of the focal point 403 and the HIFU beam 404 of the treatment probe 37a are displayed on the navigation screens 531 to 534. Each is displayed. The surgeon 29 operates the position of the ultrasonic probe 37 while looking at the navigation screens 531 to 534 to adjust the focus 403 of the treatment probe 37a to the target. For example, a three-dimensional volume rendering screen 534 can be used in addition to the navigation screens 531 to 533 having three-axis cross sections (Axial, Sagittal, and Coronal), but the navigation screen can be freely customized. In addition, the operator 29 previously sets a treatment planned area 536 that is a treatment target site, a warning area, a margin, and the like in advance. Note that the navigation image can be configured by using three-dimensional image volume data captured by a medical image apparatus such as an MRI apparatus in addition to an ultrasonic image apparatus.

In addition to the simulated image of the ultrasonic probe 37, preoperative planning (surgery simulation) information 537 can be superimposed on the navigation image. Further, in the case of the volume rendering screen 534, the treatment scheduled area 536 can be displayed three-dimensionally. Further, it is possible to provide a function of issuing a warning when entering the treatment scheduled area 536 or warning area on the navigation screens 531 to 534. In addition, for example, when the treatment scheduled area 536 enters the warning area, a function of automatically changing an image on the navigation screen and a treatment parameter can be provided.

When the above-described operation is performed inside the gantry of the MRI apparatus, the above-mentioned information is fed back continuously and in real time to the ultrasound treatment system, and the same MRI imaging including a simulated image of the ultrasound probe 37 in the treatment target region A cross-sectional image 508 and an ultrasonic image 509 can be displayed. That is, the surgeon 29 can use the two-dimensional real-time image obtained by the MRI apparatus 1 and the three-dimensional image information obtained by navigation for treatment as necessary. As one application of the high-speed imaging sequence of the MRI apparatus 1, a real-time dynamic imaging method called fluoroscopy (fluoroscopic imaging) is being clinically applied. In fluoroscopy, by repeating imaging and image reconstruction with a period of about 1 second or less, it can be used to extract the dynamics of internal tissues and grasp the position of an instrument inserted from the outside like a fluoroscopic imaging. Generate and display dynamic images. This application is also applied to three-dimensional high-speed imaging.

FIG. 8 shows a flowchart of a processing procedure of an embodiment of the ultrasonic therapy system of the present invention. First, a plurality of three-dimensional volume imaging and three-dimensional image reconstruction are performed using the MRI apparatus 1 (S1). Next, a specific area (segmentation) in which treatment is indispensable is depicted from the three-dimensional image by image processing (S2). Based on the rendered image including the specific area, the area that allows HIFU irradiation and the area that cannot be irradiated are discriminated and set (S3). Next, a treatment scheduled area and a margin area including them are set (S4). After inputting parameters necessary for HIFU irradiation (S5), the HIFU treatment plan is executed to simulate the position of the ultrasonic probe 37 (S6). After the treatment plan, the operation support guidance function such as navigation is activated (S7), and the operation is started (S8).

At the time of surgery, following the change in the position of the ultrasonic probe 37, a simulated image showing the focal position 403 of the treatment probe 37a and the HIFU beam bundle 404 that is the HIFU irradiation path is superimposed on the navigation image (S9). As a result, the operator 29 guides the ultrasonic probe 37 to the planned treatment position (target position) using the images and numerical information displayed on the monitor 38 and the GUI (S10). After the guidance, the position of the target is confirmed with an MR image (for example, a blood flow image) or an ultrasonic image (elastography) (S11).

Next, the body surface (skin) of the living body is drawn from the ultrasonic image, MR image or other medical image (S12). Next, the position of the focal point 403 is drawn from the position of the treatment probe 37a detected by the position detection device 9, and the distance from the focal point 403 to the body surface (skin) is calculated (S13). At this time, the position data of each treatment transducer 39 stored in advance is determined, and a simulated image of the treatment ultrasound beam 404a transmitted from each treatment transducer 39 and reaching the focal point 403 is at least an ultrasound image and an MR image. On the other hand, the distance from the focal point 403 to the body surface (skin) can be calculated by drawing the image on another medical image. An example of this image is shown in FIG.

Next, in step S14, the division number N of the channel group G of the channels to be irradiated by dividing the trigger ultrasonic wave and the heating ultrasonic wave is determined according to the distance from the focal point 403 to the body surface (skin) (S14). Specifically, as shown in FIG. 10, it is determined whether or not the distance L from the focal point 403 to the body surface 501 is within a preset distance range (minimum value Xmin to maximum value Xmax). For example, the division number N of the channel group G of the channel is determined according to the distance L. For example, as shown in FIGS. 10 (a) and 10 (b), sections Xmin to X1, X1 to X2, sandwiched between a plurality of distances X1, X2,..., Xm set within the range of Xmin to Xmax, ..., the division number N is set in correspondence with Xm to Xmax.

Here, the maximum value Xmax is a distance at which there is no risk of skin burns even when a heating ultrasonic wave is applied following a trigger ultrasonic wave from all of a plurality of channels. Therefore, if L> Xmax, the distance is not required to irradiate the trigger ultrasonic wave and the heating ultrasonic wave separately. That is, the therapeutic ultrasound beam 404a heading from each channel toward the focal point is formed in a tapered pyramid shape as it approaches the focal point 403. Therefore, as the focal point 403 is approached, the cross-sectional area of the therapeutic ultrasonic beam 404a is reduced, and the energy density of the therapeutic ultrasonic beam 404a is increased. Therefore, there is a risk of skin burns as the position of the body surface 501 approaches the focal point 403. On the other hand, the maximum value Xmax is set based on the fact that the body surface 501 is far away from the focal point 403 and the energy density of the treatment ultrasonic beam 404a on the body surface is so low that there is no possibility of causing skin burns. Instead of the maximum value Xmax, conversely, the minimum value of the distance from each channel of the treatment probe 37a to the body surface 501 is set, and if the distance from each channel to the body surface 501 is equal to or less than the minimum value, It may be determined that the energy density of the therapeutic ultrasound beam 404a is low enough not to cause skin burns.

Also, the minimum value Xmin is a distance that may cause skin burn even when the trigger ultrasonic wave and the heating ultrasonic wave are divided and irradiated. That is, when the body surface 501 is close to the focal point 403 and is equal to or less than the minimum value Xmin, not only the energy density of the therapeutic ultrasound beam 404a is increased, but also the wavefront of the trigger ultrasound or heating ultrasound emitted from a plurality of channels is used. The degree of coincidence increases and the intensity of the therapeutic ultrasound beam 404a increases. For this reason, even if the channel for irradiating the trigger ultrasonic wave and the channel for irradiating the heating ultrasonic wave are differentiated and divided irradiation is performed, this is the distance where the possibility of skin burn remains.

Returning to FIG. 8, for each of the plurality of channel groups G divided in step S14, for each treatment ultrasound cycle, the channel group G is switched to irradiate the trigger ultrasound, and then all the remaining channel groups G are irradiated. Start HIFU treatment with heating ultrasound. At the same time, monitoring is performed with MR images or ultrasonic diagnostic images, and the progress of treatment is recorded as appropriate (S15). The treatment process by the treatment ultrasonic cycle is repeated a plurality of times for each focal point 403 of the treatment target region, and after confirming the treatment effect (S16), the necessity of additional treatment is confirmed (S17), and if additional treatment is necessary, step S9 If it is not necessary, the process ends (S18). Note that the processing from steps S12 to S14 in FIG. 8 is executed by the HIFU controller 49, which is a treatment probe control unit.

Next, with reference to FIG. 9, a detailed processing procedure of step S14 described above among the processing executed by the HIFU controller 49 will be described. It is determined whether or not the distance L from the focus 403 calculated in step S13 to the body surface 501 is equal to or greater than a maximum value Xmax of a predetermined distance range (S21). If it is determined in step S21 that L ≧ Xmax, the process proceeds to step S22 to notify the user of setting conditions related to the HIFU treatment by image information or audio information to prompt the final judgment or determination of the treatment. Return to S15. That is, if L ≧ Xmax, it is allowed to repeatedly irradiate the focal point 403 with HIFU composed of trigger ultrasound and heating ultrasound from all channels. In this specification, the HIFU of FIG. 5 consisting of trigger ultrasound and heating ultrasound is referred to as a basic treatment ultrasound cycle.

On the other hand, if it is determined in step S21 that the distance L is less than the maximum value Xmax, it is determined whether or not the distance L is less than the minimum value Xmin that may cause a burn on the body surface (skin) (S23). If this determination is L ≦ Xmin, the user is notified that HIFU irradiation is not possible, and the movement of the treatment probe 37a is recommended (S24), and the process proceeds to step S9.

Also, if the distance L is less than the maximum value Xmax as determined in step S21 and the distance L is greater than the minimum set value Xmin as determined in step S23, that is, if Xmin <L <Xmax, If the trigger ultrasonic wave and the heating ultrasonic wave are continuously irradiated from all, the skin may be burned. Therefore, the present invention in which the trigger ultrasonic wave and the heating ultrasonic wave are divided and irradiated from different channels is applied to avoid skin burns (S25).

Next, in step S26 of FIG. 9, the therapeutic ultrasonic energy irradiated to the focal point 403 is compensated for the basic therapeutic ultrasonic energy which is a target value. That is, if the trigger ultrasonic wave and the heating ultrasonic wave are divided and irradiated from different channels, there is a channel that does not irradiate the trigger ultrasonic wave or the heating ultrasonic wave, so that the therapeutic ultrasonic energy irradiated to the focal point 403 decreases. Even when such a divided therapeutic ultrasonic cycle is repeated, the time for the therapeutic ultrasonic energy irradiated to the focal point 403 to reach the target value becomes longer. Therefore, in step S26, compensation processing is performed to increase the unit therapeutic ultrasonic energy irradiated from each channel so that the therapeutic ultrasonic energy irradiated to the focal point 403 is maintained at the target value.

Next, in step S26, the therapeutic ultrasonic energy (intensity) of each channel after compensation is compared with a predetermined upper limit value Ecmax to determine whether or not there is a possibility of skin burns. If there is a concern about skin burns, the process proceeds to step S28, notifying the user that HIFU irradiation is not possible, recommending movement of the treatment probe 37a, and proceeding to step S9. On the other hand, even if the intensity of the treatment ultrasound for each channel is compensated, if there is no concern about skin burns, the user is notified of the condition after the setting change and prompts the final decision on treatment (S22).

Hereinafter, the split irradiation of the trigger ultrasonic wave and the heating ultrasonic wave and the compensation of the therapeutic ultrasonic energy for each divided channel unit according to the feature of the present invention will be described in detail based on examples.

(Split irradiation of trigger ultrasound and heating ultrasound)
FIG. 12 shows an embodiment of the present invention in which a plurality of n channels of the treatment probe 37a are divided into a channel group G including a plurality of m channels, and a trigger ultrasonic wave and a heating ultrasonic wave are divided into the channel group G and irradiated. 1 is shown. In FIG. 10 (a), if the distance L from the focal point 403 to the body surface 501 is within the range of Xmin <L <Xmax, a channel including a plurality of n channels according to the distance L is included. Divide into groups G ₁ to G ₄ . A plurality of intermediate distances Xi (i is a natural number) are set in the range of Xmin to Xmax, and the division number N (n / m) of the channel group G is uniquely determined for each distance section Xi to which the distance L belongs. Set it. For example, when the distance L belongs to the distance section of X ₂ to Xmax, the treatment probe 37a includes a plurality of n channels (n = 40 in the illustrated example) and a plurality of m channels (m = 10 in the illustrated example). Divide into N (= n / m) fan-shaped channel groups G ₁ to G ₄ . As a result, as in the first embodiment shown in FIG. 12, the division number (N = 4) of the channel group G to which the trigger ultrasonic wave is divided and irradiated is set. In the first embodiment, an example in which a plurality of adjacent fan-shaped channels are included in one channel group G is shown, but the present invention is not limited to this, and each channel group G If set so as to include m channels, the channel group G can be divided and set including channels that are not adjacent to each other. The division of the channel group G is automatically performed according to a procedure set in advance by the HIFU controller 49.

Then, as shown in FIG. 12 (a), it is irradiated with trigger ultrasound from respective m (= 10) all channels belonging to the channel group G ₁ including a number of channels. Subsequently, heating ultrasonic waves are applied from the remaining three (N-1) channel groups G ₂ to G ₄ shown in FIG. Next, trigger ultrasonic waves are irradiated from all channels belonging to the channel group G ₂ , and subsequently, heated ultrasonic waves are irradiated from the remaining channel groups G ₁ , G ₃ to G ₄ . In this way, the channel groups G ₁ → G ₂ → G ₃ → G ₄ to which the trigger ultrasonic waves are irradiated are sequentially switched, and heating is performed from the remaining G (N−1) channel groups that are not irradiated with the trigger ultrasonic waves. Irradiate with ultrasonic waves. That is, in Example 1, the basic treatment ultrasonic cycle shown in FIG. 5 is divided into different channel groups by the divided treatment ultrasonic cycle in which the pulsed trigger ultrasonic wave 801 and the continuous wave heating ultrasonic wave 802 are separated. Divide and irradiate from G ₁ to G ₄ . Thereby, skin burns can be avoided and therapeutic ultrasound can be irradiated to the focal point. It goes without saying that the split treatment ultrasound cycle is repeated until the treatment ultrasound energy irradiated to the focal point 403 reaches a target value.

Further, the division number N of the channel group G can be obtained using a graph set as shown in FIG. 11 (a), for example. In FIG. 4A, the horizontal axis represents the distance L from the focal point to the body surface, and the vertical axis represents the division number N of the channel group G. A curve in the figure is a setting curve 104 set in advance in order to determine the division number N (= n / m) of the channel group G according to the distance L. Therefore, the division number N of the channel group G on the vertical axis at the point 105 on the setting curve 104 corresponding to the distance L on the horizontal axis in FIG.

On the other hand, in the example shown in FIG. 10 (a), when the distance L belongs to the distance section of X ₂ to Xmax, the division number N of the channel group G may be set to 1/4 in advance. As a result, the division number N of the channel group G on which the trigger ultrasonic waves are divided and irradiated automatically can be determined by the HIFU controller 49.
(Compensation of therapeutic ultrasonic energy for each channel)
Here, compensation of therapeutic ultrasonic energy, which is reduced by splitting and irradiating trigger ultrasonic waves and heating ultrasonic waves from different channels, will be described based on examples. Now, as in Example 1 of FIG. 12, it is divided into _four channel groups G ₁ to G ₄ and further irradiated with trigger ultrasonic waves from _one channel group (for example, G ₁ ), and the remaining channel groups When heating ultrasonic waves are separated from (for example, G ₂ to G ₄ ) and irradiated, the treatment ultrasonic energy irradiated to the focal point 403 is equal to the trigger ultrasonic wave 801 and the heating ultrasonic wave 802 of the basic therapeutic ultrasonic cycle. Decrease. Specifically, the energy of the trigger ultrasonic wave is reduced to (1 / N = 1/4), and the energy of the heating ultrasonic wave is reduced to (N−1 / N) = 3/4. Thus, the energy of the trigger ultrasonic wave is multiplied by 4 and the energy of the heated ultrasonic wave is multiplied by 4/3, so that the energy of the target basic treatment ultrasonic cycle can be irradiated (injected) to the focal point 403. In other words, a plurality of n channels are divided into a plurality of N channel groups G having a plurality of m channels, and further, a trigger ultrasonic wave is irradiated from one channel group G, and heating is performed from the remaining (N-1) channel groups G. The therapeutic ultrasound cycle that splits and irradiates the ultrasound is less than the energy of the basic therapy ultrasound cycle.

Therefore, in order to compensate the therapeutic ultrasonic energy input to the focus to the target value, it is necessary to compensate for the increase of the therapeutic ultrasonic energy for each channel. here,
Trigger ultrasonic energy: e ₁ (per unit time)
Heating ultrasonic energy: e ₂ (per unit time)
Trigger time: t ₁
Heating time: t ₂
PRF: (= initial set value x any natural number multiple)
Frequency adjustment factor: k (initial value = 1, any natural number)
Total number of channels: n
Number of channels in channel group G: m
Number of divisions of channel group G: N (= n / m)
It is defined as

As described above, assuming that the ultrasonic wave transmission area of each channel is equal, the therapeutic ultrasonic energy E of each channel unit of the divided therapeutic ultrasonic cycle can be expressed by Expression (1).

E = [{(e ₁ × t ₁ ) 1 / N}
+ {(E ₂ × t ₂ ) × (N−1) / N}] PRF (1)
In other words, the treatment ultrasonic energy E of each channel alone is reduced to 1 / N according to the division number N of the channel group G that irradiates the trigger ultrasonic wave, and the heating ultrasonic energy (N− 1) Reduced to / N. This decrease can be compensated for, for example, by multiplying the energy of the trigger ultrasonic wave by N and multiplying the intensity of the heated ultrasonic wave by N / (N−1), as shown in equation (2). Ec is the therapeutic ultrasonic energy compensation value of a single channel.

Ec = [{(e ₁ × t ₁ ) 1 / N} × N
+ {(E ₂ × t ₂ ) × (N−1) / N} × 1 / N] PRF (2)
A setting curve 104 in FIG. 11A is a graph of Expression (2).

The therapeutic ultrasonic energy compensation value Ec of each channel unit of the present invention is not limited to the above formula (2), but the frequency of the trigger ultrasonic wave is changed as shown by Ec ′ shown in the following formula (3). Also good. When the frequency adjustment coefficient k of the trigger ultrasound is changed, the trigger time t ₁ becomes 1 / k, and when the treatment ultrasound cycle time is constant, the heating time t ₂ is automatically changed to t ₃ .

Ec ′ = {(e ₁ × t ₁ / k) + (e ₂ × t ₃ )} PRF (3)
According to this, the trigger ultrasonic energy becomes 1 / k, and is compensated to Ec ′ = E × 96%, which is substantially equivalent to the ultrasonic energy E of the basic treatment ultrasonic cycle. By compensating the treatment ultrasonic energy for each channel in this way, the skin damage on the body surface is reduced to 1 / N while keeping the treatment ultrasonic energy irradiated (injected) at the focal point the same or almost the same. it can. Further, by compensating the energy of the trigger ultrasonic wave 801 and the heating ultrasonic wave 802, it is possible to suppress an increase in the HIFU treatment time.

The compensation of therapeutic ultrasonic energy for each channel can be automatically performed by the HIFU controller 49 according to the setting curve 106 shown in FIG. In FIG. 5B, the horizontal axis represents the division number N of the channel group G that irradiates the trigger ultrasonic wave, and the vertical axis represents the ultrasonic intensity (energy) of the channel alone. The curve in the figure is a setting curve 106 set in advance to determine the ultrasonic intensity (energy) of a single channel corresponding to the division number N of the channel group G.

Corresponding to the distance L from the focal point 403 to the body surface 501, the setting curve 104 in FIG. An intersection 107 with the setting curve 106 corresponding to the division number N of the channel group G to be irradiated with the trigger ultrasound on the horizontal axis is obtained. The therapeutic ultrasonic energy E (or E ′) of each channel unit on the vertical axis corresponding to the intersection 107 is obtained. Note that Emax on the vertical axis in FIG. 11 (b) is the upper limit value of the treatment ultrasonic energy E in units of channels, and the trigger ultrasonic energy equal to or higher than Emax is a value that may cause spot-like body surface burns. Is set. Therefore, the intersection 108 with the setting curve 106 corresponding to Emax corresponds to the division number Nmax of the maximum channel group G that cannot further divide the channel group G. Therefore, the hatched area in FIG. 11 (b) is a range where HIFU irradiation is possible. If it is within this range, a message “HIFU irradiation is possible” is finally displayed to the user, and HIFU treatment is performed according to the user instruction.

According to the first embodiment, a plurality of channels are divided into four channel groups G, the trigger ultrasonic waves are irradiated from the channels of one channel group G to the focal point, and the remaining three channels are continued after the trigger ultrasonic waves. Since the heating ultrasonic wave is irradiated to the focal point from the channel of group G, and then the channel group G to which the trigger ultrasonic wave is irradiated is switched, the treatment ultrasonic cycle is repeated in the same manner, so that damage due to burns on the body surface etc. It can be reduced to 1/4 (= 1 / N). As a result, the trigger ultrasonic wave and the heating ultrasonic wave can be irradiated to the focal point without being interrupted by skin burns on the body surface, so that the HIFU treatment efficiency can be improved and the treatment accuracy can be improved.

Also, in the split treatment ultrasound cycle, the treatment ultrasound energy input to the focal point is reduced by the amount corresponding to the channel group G that is not irradiated with the trigger ultrasound or the heating ultrasound. In this regard, according to the present embodiment, since the treatment ultrasonic energy that is reduced by the divided irradiation is compensated, the treatment ultrasonic energy is increased and compensated for each channel unit, so that skin burn can be avoided, In addition, it is possible to suppress the lengthening of the HIFU treatment time.

FIG. 13 shows a second embodiment of the present invention in which the division form of the channel group G of the first embodiment is changed. This embodiment is the same in that a plurality of n (= 40) channels are divided into a plurality of N (= 4) channel groups G composed of a plurality of m (= 10) channels. In the present embodiment, as shown in FIG. 13, unlike the first embodiment, the positions of the channels of a plurality of m (= 10) channels are two fan-shaped regions whose center angle positions of the treatment probe 37a are shifted from each other as the channel group G. Yes. In other words, the channel group G is composed of a plurality of m channels included in the two fan-shaped regions. According to the present embodiment, the same effect as in the first embodiment can be obtained. Furthermore, according to the present embodiment, since the channel group G is separated in the phase angle direction (circumferential direction) between the two fan-shaped regions irradiated with the trigger ultrasonic waves, it is possible to reduce damage in adjacent regions.

FIG. 14 shows a third embodiment of the present invention in which the division form of the channel group G of the first embodiment is changed. This embodiment is the same in that a plurality of n (= 40) channels are divided into a plurality of N (= 4) channel groups G composed of a plurality of m (= 10) channels. In the first embodiment, the channels of two adjacent fan-shaped regions are divided as a channel group G. In this embodiment, a part of the channel group G composed of two adjacent fan-shaped regions (two channels on the center side) is shifted in the circumferential direction, that is, the channel in the central region and the channel in the outer region are shifted in the circumferential direction. It is a feature. According to the present embodiment, the same effect as in the first embodiment can be obtained.

In FIG. 15, a plurality of n channels of the treatment probe 37a according to the fourth embodiment of the present invention are divided into a channel group G including a plurality of m channels, and a trigger ultrasonic wave and a heating ultrasonic wave are divided into the channel group G. The figure to irradiate is shown. In the present embodiment, n = 40 as in the first embodiment, but differs from the first embodiment in that the division number N of the channel group G is set to 8 and m = 5. In the present embodiment, the distance L falls within the range of Xmin <L <X2, as shown in FIG. 10 (b). That is, since the body surface 501 is closer to the focal point 403 than in the first embodiment, the number of divisions N of the channel group G is increased to avoid skin burns. In this embodiment, as shown in FIG. 16, a plurality of n channels are radially divided into N = 8 channel groups G each consisting of m = 5 channels, and the trigger ultrasonic waves are divided into eight channel groups G. And then irradiate.

Further, in the present embodiment, as indicated by the arrows in the figure, the order of the channel group G that irradiates the trigger ultrasound according to the divided therapy ultrasound cycle is not the phase of the adjacent channel group G but the phase of the concave spherical surface of the ultrasound probe 37a. The channel group G is 180 ° apart in angle. Thereby, damage to the body surface corresponding to the adjacent channel group G can be reduced.

In addition, according to the present embodiment, the treatment ultrasonic energy for each channel is compensated for by heating the ultrasonic wave by compensating the trigger ultrasonic energy by multiplying the amplitude of the trigger ultrasonic wave by 8 as shown in Equation (2). It is necessary to supplement the heating ultrasonic energy by multiplying the amplitude of the sound wave by 8/7. Also, as shown in FIG. 15, the split therapy ultrasound cycle will be repeated at least 8 times.

FIG. 16 shows a diagram in which the trigger ultrasonic wave and the heating ultrasonic wave according to the fifth embodiment of the present invention are divided into channel groups G and irradiated. The present embodiment is different in that the division form of the channel group G in the first or third embodiment is different. That is, this embodiment is the same in that a plurality of n (= 40) channels are divided into a plurality of N (= 4) channel groups G composed of a plurality of m (= 10) channels. However, each channel group G is configured by appropriately shifting the positions of ten channels belonging to one channel group G in the phase direction (circumferential direction). In other words, the channel group G is configured by selecting channels arranged in a circle from the outside toward the center. Thereby, even if the trigger ultrasonic wave is irradiated for each channel group G, since there are few adjacent channels, damage to the body surface by the channel group G irradiated with the trigger ultrasonic wave can be reduced.

FIG. 17 shows a diagram in which the trigger ultrasonic wave and the heating ultrasonic wave according to the sixth embodiment of the present invention are divided into channel groups G and irradiated. The present embodiment is different from the fourth embodiment in that the channel group G in the fourth embodiment shown in FIG. According to the present embodiment, since channels belonging to one channel group G are not in contact with each other, damage to the body surface by the channel group G irradiated with the trigger ultrasonic wave can be further reduced or completely eliminated. Further, according to the present embodiment, as indicated by the arrows in the figure, the order of the channel group G to which the trigger ultrasound is irradiated can be arranged in the arrangement of the concave spherical surface of the ultrasonic probe 37a instead of the adjacent channel group G. The channel group G is as far away as possible. Thereby, damage to the body surface corresponding to the adjacent channel group G can be reduced.

FIG. 18 shows a seventh embodiment in which the trigger ultrasonic wave and the heating ultrasonic wave of the present invention are divided into channel groups G. The present embodiment is characterized in that a plurality of n (= 40) channels of the treatment probe 37a are divided into N (= 20) channel groups G including a plurality of m (= 2) channels. According to this embodiment, since the number of divisions is increased, damage to the body surface can be reduced to 1/20 accordingly. However, on the contrary, the treatment ultrasonic energy compensation for each channel unit compensates the trigger ultrasonic energy by multiplying the amplitude of the trigger ultrasonic wave by 20, for example, as shown in the equation (2). It is important to adopt in consideration of the effect of sound pressure due to ultrasonic waves on the body surface and the like. For example, considering the extension of the trigger time (irradiation time) and the compensation of the amplitude, the damage to the skin can be reduced and the minimally invasive can be realized while maintaining the therapeutic effect.

As described above, the features of the present invention in which the trigger ultrasonic wave and the heating ultrasonic wave are divided and irradiated based on the embodiment have been described. In short, the present invention divides a plurality of channels (therapeutic transducer 39) into a channel for irradiating a trigger ultrasonic wave and a channel for irradiating a heating ultrasonic wave, and irradiates the trigger ultrasonic wave every time the treatment ultrasonic cycle is repeated. It is characterized by switching channels to be performed. In other words, when trigger ultrasonic waves are irradiated from one channel and subsequently heated ultrasonic waves are irradiated from the same channel, bubbles generated by the trigger ultrasonic waves are destroyed by the heated ultrasonic waves, and the heat of bubble destruction is generated. In view of the above, the present invention is characterized in that the channels for transmitting the trigger ultrasonic wave and the heating ultrasonic wave are different. In other words, the propagation path (ultrasonic beam) of the trigger ultrasonic wave in the vicinity of the body surface and the propagation path (ultrasonic beam) of the heating ultrasonic wave are made different for each treatment ultrasonic cycle. As a result, while the pulsed trigger ultrasound is irradiated on or near the body surface, it is extremely short (for example, on the order of μsec), and the heating time of the heating ultrasound is longer than that of the trigger ultrasound. In the sonic cycle, since the bubbles disappear before the heating ultrasonic waves are irradiated, the bubbles are not destroyed by the heating ultrasonic waves.

Further, when the trigger ultrasonic wave and the heating ultrasonic wave are divided and irradiated as in the present invention, the focal point is irradiated from each channel compared to the case where the trigger ultrasonic wave and the heating ultrasonic wave are irradiated to the focal point from all channels. The therapeutic ultrasonic energy per therapeutic ultrasonic cycle decreases. Therefore, when carrying out the present invention, the HIFU controller 49, which is a treatment probe control unit, matches the trigger ultrasonic wave constituting the treatment ultrasonic cycle according to the target value of the treatment ultrasonic energy irradiated toward the focal point 403. Compensates for the ultrasonic energy of the heated ultrasound. The target value of therapeutic ultrasonic energy can be the basic therapeutic ultrasonic energy that irradiates the focused ultrasonic wave toward the focal point 403 following the trigger ultrasonic wave from each channel.

The HIFU controller 49 measures the distance L from the focal point 403 to the body surface 501 of the living body, and performs divided irradiation when the distance L is within a predetermined minimum value Xmin to maximum value Xmax 最大. When the distance L exceeds the maximum value Xmax, it is possible to perform basic irradiation that irradiates the heating ultrasonic wave toward the focal point following the trigger ultrasonic wave from all channels instead of the divided irradiation.

Further, the arrangement configuration image of the plurality of channels of the treatment probe 37a is displayed on the monitor 38, and the channel that irradiates the trigger ultrasonic wave toward the focal point 403 is different from the channel that irradiates the heating ultrasonic wave toward the focal point 403. It is preferable to display in a display form. According to this, the user can easily confirm the content of the divided irradiation.

FIG. 19 shows a GUI display example at the time of surgery / treatment of the present invention. When the 3D imaging button 1201 is pressed, the Axial section 1231, Sagittal section 1232, Coronal section 1233, and Volume Rendering screen 1234 are reconfigured. Is done. Further, by depressing the HIFU irradiation enable / disable area setting button 1203, the ultrasound access disabled area 1240 is identified in addition to the area 1219 to be treated with respect to the drawn segmentation information. In addition, by pressing the treatment plan / margin setting button 1204, the treatment route 1238 can be calculated in advance, and guidance can be provided along the treatment route.

These information can be freely rotated on the Volume Rendering screen 1234, and can be viewed from another viewpoint / angle. In addition, a target 1219 that is a tumor region (treatment region) and a margin region 1220 including them are set. Here, by pressing a treatment parameter setting button 1205, a treatment parameter for the region can be input. Specific input values include the type, shape, output intensity, and unit output intensity for each channel of the ultrasonic probe 37. At the time of actual surgery, by pressing a navigation button 1206, a surgical support function such as equipment necessary for treatment and navigation operates in conjunction with each other. The position of the HIFU probe 37 is detected and superimposed on the Axial section 1231, the Sagittal section 1232, the Coronal section 1233, and the VolumeingRendering screen 1234.

The surgeon guides the ultrasonic probe 37 with reference to the treatment path 1238 obtained in advance. In addition, the past path of the ultrasonic probe 37 can be displayed, and the information screen 1225 displays the difference between the tumor area and the treatment area as the log information in addition to the treatment progress / biological information, the number of treatments, the time, the ratio, the number of remaining treatments. The schedule can also be displayed in real time as surgery information. Immediately before treatment, the channel group division calculation button 1207 is pressed to measure the distance from the HIFU focal point 403 to the surface 501, and the channel group is divided using the graph of FIG. To compensate. The calculation result is displayed not only as the number of divisions 1212 as the probe information 1211 but also as an animation display 1213 using a preset parameter 1214.

Here, when there is an ultrasound path in the ultrasound inaccessible area 1240, it also has a warning function that prompts the probe to change its position. By displaying these information on the navigation image immediately before the treatment, the information is visually transmitted to the user. By pressing the HIFU irradiation / effect confirmation button 1208, the treatment ultrasound 702 and the image ultrasound 601 are alternately illuminated, and the treatment area 1218 for the target 1219 is displayed in real time on the treatment information / ultrasound image, Various information and warning information can also be displayed on the treatment image.

For example, a previously treated area 1218 that has been treated in the past is displayed in a superimposed manner, and a function that issues a warning when the planned margin area 1220 is exceeded or an abnormality occurs in the patient is automatically turned ON / OFF. You can also. In addition to the target 1219, “remaining treatment area = target 1219−treated area 1218” and a margin 1220 are also displayed, so that the operator can visually recognize the remaining treatment area, and MR imaging and It also has a function of imaging alternately in conjunction with ultrasonic imaging. On the MR image, the specific area, the margin area, and the ARFI treatment planned area are displayed in the same manner, and images with different tissue contrasts are displayed.

The user determines whether to perform retreatment from the image information before and after treatment 1231-1234 and the operation information 1225, and retreats as necessary. Another advantage of MRI is that it can be imaged deep into the body. As a result, the surgeon can move the surgical tool and perform additional treatment while viewing the previous treatment image. The information before and after the treatment can be linked with the operation information 1225 in addition to the ultrasonic image 1217, the triaxial cross sections 1231 to 1233, the Volume Rendering image 1234, and the MRI image.

¡The therapeutic ultrasound probe supports not only manual operation but also machine operation using a manipulator. The position information may be acquired from the position detection device 9 or may be displayed as the three-dimensional displays 1231 to 1234 using the coordinates of the manipulator.

As mentioned above, although this invention was demonstrated based on one Embodiment, this invention is not limited to these, It is possible to implement in the form deform | transformed or changed in the range of the main point of this invention. It will be obvious to those skilled in the art, and it is obvious that such modifications or alterations belong to the scope of the claims of the present application.

1 MRI machine, 3 Upper magnet, 5 Lower magnet, 7 posts, 9 Position detection device, 11 Arm, 13, 14 Monitor, 15 Monitor support, 17 Reference tool, 19 Personal computer, 21 Bed, 23 MRI control, 24 Patient, 25 Infrared camera, 27 Pointer, 29 Operator, 33 RS232C cable, 34 Video recording device, 35 Reflective sphere, 37 Ultrasonic probe, 38 Monitor, 40 Ultrasonic therapy device, 49 HIFU controller, 50 Power amplifier, C channel _{_{, G 1, G 2, G}} 3, G 4 group of channels

Claims

A treatment probe having a plurality of channels including treatment transducers for generating treatment ultrasound, and a focus set from the treatment probe to a treatment target site of a living body, followed by a trigger ultrasound and an intensity higher than the trigger ultrasound. A treatment probe controller that repeats a treatment ultrasound cycle that irradiates weakly heated ultrasound,
The treatment probe control unit divides the channel for irradiating the trigger ultrasonic wave toward the focal point and the channel for irradiating the heated ultrasonic wave toward the focal point for each treatment ultrasonic cycle. An ultrasonic therapy apparatus characterized by performing irradiation.
The therapeutic probe control unit compensates the ultrasonic energy of the trigger ultrasonic wave and the heating ultrasonic wave that constitute the therapeutic ultrasonic cycle according to a target value of therapeutic ultrasonic energy irradiated toward the focal point. 2. The ultrasonic therapy apparatus according to claim 1, wherein:
3. The target value of the therapeutic ultrasonic energy is basic therapeutic ultrasonic energy that irradiates the heated ultrasonic wave toward the focal point following the trigger ultrasonic wave from each channel. Ultrasound therapy device.
The treatment probe control unit measures the distance from the focal point to the body surface of the living body, and performs the divided irradiation when the measurement distance is within a predetermined minimum value and maximum value range, and the measurement distance When the value exceeds the maximum value, instead of the divided irradiation, basic irradiation is performed by irradiating the heating ultrasonic wave toward the focal point following the trigger ultrasonic wave from all the channels. The ultrasonic therapy apparatus according to claim 1.
The monitor further includes a monitor that displays an arrangement image of a plurality of channels of the treatment probe, and the monitor irradiates the trigger ultrasonic wave toward the focal point and the heating ultrasonic wave toward the focal point. 2. The ultrasonic therapy apparatus according to claim 1, wherein the channel to be irradiated is displayed in a different display form.
The therapeutic probe has a hemispherical concave surface divided into a plurality of concentric annular regions, and each channel is formed in each of a plurality of regions obtained by dividing the annular region in the radial direction. 2. The ultrasonic therapy apparatus according to claim 1, wherein the ultrasonic transmission surface of each has an equal area.
The treatment probe control unit divides the plurality of channels into a plurality of channel groups, irradiates the trigger ultrasonic waves from the channels belonging to one channel group toward the focal point, and subsequently to the other channel groups. The treatment ultrasonic cycle for irradiating the heating ultrasonic wave from the channel to which it is directed toward the focal point is repeated, and one channel group for irradiating the trigger ultrasonic wave for each repetition of the treatment ultrasonic cycle is assigned to the other channel. 2. The ultrasonic therapy apparatus according to claim 1, wherein the apparatus is switched to one of a group.
The therapeutic probe control unit adjusts at least one of the amplitude, frequency, or irradiation time of the trigger ultrasonic wave, or the amplitude, frequency of the heating ultrasonic wave in accordance with a target value of therapeutic ultrasonic energy irradiated toward the focal point. 8. The ultrasonic therapy apparatus according to claim 7, wherein the ultrasonic energy is compensated by adjusting at least one of the irradiation times.
9. The target value of the therapeutic ultrasonic energy is reference therapeutic ultrasonic energy for irradiating the heated ultrasonic wave toward the focal point from the channels following the trigger ultrasonic wave. Ultrasound therapy device.
The treatment probe control unit measures the distance from the focal point to the body surface of the living body, and performs the divided irradiation when the measurement distance is within a predetermined minimum value and maximum value range, and the measurement distance When the value exceeds the maximum value, instead of the divided irradiation, basic irradiation is performed by irradiating the heating ultrasonic wave toward the focal point following the trigger ultrasonic wave from all the channels. The ultrasonic therapy apparatus according to claim 7.
When the number of the plurality of channels is n and the number of the plurality of channels of the channel group is m, the treatment probe control unit multiplies the amplitude of the trigger ultrasonic wave by n / m, or the trigger 9. The ultrasonic therapy apparatus according to claim 8, wherein the therapeutic ultrasonic energy is compensated by adjusting the trigger ultrasonic energy by multiplying an ultrasonic frequency by an integer.
When the therapeutic probe energy compensates the therapeutic ultrasonic energy, if the energy of the trigger ultrasonic wave or the energy of the heating ultrasonic wave exceeds a preset upper limit value, a warning to that effect is made by voice, sound or image 9. The ultrasonic therapy apparatus according to claim 8, which is notified by information.
13. The ultrasonic therapy apparatus according to claim 12, wherein the upper limit value is set to a value for preventing a burn on the body surface of the living body located between the channel and the focal point.
A treatment probe having a plurality of channels including treatment transducers for generating treatment ultrasound, and a focus set from the treatment probe to a treatment target site of a living body, followed by a trigger ultrasound and an intensity higher than the trigger ultrasound. A treatment probe controller that repeats a treatment ultrasound cycle that irradiates weakly heated ultrasound, and a plurality of imaging transducers that are provided at the center of the treatment probe and that transmit and receive ultrasound for imaging with the living body An imaging probe comprising: an ultrasound image forming unit that generates an ultrasound image including the focus generated from a reception signal of the imaging probe; and a display unit that displays the ultrasound image.
The treatment probe control unit divides the channel for irradiating the trigger ultrasonic wave toward the focal point and the channel for irradiating the heated ultrasonic wave toward the focal point for each treatment ultrasonic cycle. An ultrasonic treatment system characterized by performing irradiation.
Furthermore, a three-dimensional position detector for detecting the position of the treatment probe, a memory in which three-dimensional volume image data including the treatment target portion of the living body is stored, and the three-dimensional position detector A medical image device having a navigation image configuration unit that generates a navigation image corresponding to a tomographic plane of the ultrasonic image from the three-dimensional volume image data based on the position of the treatment probe and displays the navigation image on the display unit;
The medical imaging apparatus includes a therapeutic ultrasound beam rendering unit that generates a simulated image of a therapeutic ultrasound beam that connects each channel and the focal point, and overlays the rendered image on the navigation image.
The treatment probe control unit measures a distance from the focal point to the body surface of the living body based on the ultrasonic image displayed on the display unit, and the measurement distance is a predetermined minimum value and maximum value. When the divided irradiation is performed within the range, and the measurement distance exceeds the maximum value, instead of the divided irradiation, the heating ultrasonic wave is transmitted from all the channels following the trigger ultrasonic wave. 15. The ultrasonic therapy system according to claim 14, wherein basic irradiation for irradiating toward a focal point is performed.