JP2009011584A - Ultrasonic therapy apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To precisely detect movement information of a cautery region in an ultrasonic therapy in a short period of time. <P>SOLUTION: The cautery region movement area setting part 7 of an ultrasonic therapy apparatus 100 sets a three-dimensional cautery region including a region to be treated on the basis of volume data of a reference respiratory phase collected from a patient and further sets the movement area of the cautery region on the basis of volume data collected time sequentially in a plurality of respiratory phases following the reference respiratory phase. Next, in irradiating the prescribed cautery position of the cautery region with strong ultrasonic waves according to a cautery plan set on the basis of the volume data of the reference respiratory phase, a cautery region movement detection part 8 detests the movement information on the cautery region by performing arithmetic operation processing of the two volume data collected in the respective adjacent respiratory phases within the range of the movement area. An ultrasonic radiation part 3 radiates the cautery position corrected on the basis of the detection result with the strong ultrasonic waves. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to an ultrasonic therapy apparatus, and more particularly to an ultrasonic therapy apparatus that performs cauterization treatment by irradiating a treatment target site with intense ultrasonic waves while observing image data.

  In recent years, a treatment method called a minimally invasive treatment has attracted attention, and an active attempt has been made in the field of malignant tumor treatment. Especially in the case of malignant tumors, most of the treatment relies on surgical operation. However, in the case of conventional surgical treatment, that is, when performing extensive tissue resection, the original function and appearance of the organ In many cases, the form is greatly impaired, and even if it is alive, a great burden is placed on the patient.

  In contrast to such conventional surgical treatment, there are a percutaneous puncture method and an extracorporeal cauterization treatment method as a minimally invasive treatment method considering QOL (quality-of-life). The former includes PEIT (Percutaneous Ethanol Injection Technique) and microwave puncture cauterization, for example, real-time images collected by the ultrasound diagnostic device showing the state of the puncture needle inserted into the patient's body. By confirming under observation of data, safety in treatment can be dramatically improved. In particular, so-called radiofrequency ablation (RFA), in which a treatment target site is cauterized by radio waves radiated from the tip of the inserted puncture needle, is easy and reliable in local ablation areas. Therefore, it has been widely used in clinical settings as a treatment method for liver tumors. However, it is becoming clear that the above-mentioned percutaneous puncture method has risks such as complications associated with puncture and seeding of cancer cells.

  On the other hand, the HIFU (High Intensity Focused Ultrasound) method, which is a treatment method for extracorporeal cauterization, focuses on the target site of treatment such as a tumor through the patient's body surface. This is a treatment that causes heat degeneration (cauterization) of the site. This treatment method is excellent in energy convergence and depth of penetration, so that it is possible to treat from outside the body to the local treatment target site that exists deep in the body, and it is necessary to insert a puncture needle. Therefore, there is an advantage that risks such as complications associated with puncture and cancer cell seeding as described above can be avoided.

  When applying the above-described HIFU method to a treatment target site such as a malignant tumor, usually, a margin area of a predetermined size is set around the treatment target site, and intense ultrasonic waves are irradiated to the treatment target site and the margin area. Prevents recurrence due to residual tumor cells.

  In the HIFU method, for example, in order to efficiently cauterize a region to be treated and its marginal region (hereinafter collectively referred to as an ablation site), a focused superstructure having a diameter of about several mm is used. A sound beam is used as a powerful ultrasonic wave. For this reason, if a position shift occurs between the ablation site and the focal point of the focused ultrasound beam due to respiratory movement, the frequency of intense ultrasound irradiation to the ablation site decreases, so a lot of time is required for ablation treatment. In addition, there is a problem that the normal tissue existing around the ablation site is damaged.

In order to solve such a problem, the above-described cauterization treatment is performed under the observation of image data collected by an ultrasonic diagnostic apparatus or the like, and in this image data, the coincidence between the ablation site and the focal point of intense ultrasound is detected. A method of irradiating intense ultrasonic waves to the ablation site when confirmed is proposed (for example, see Patent Document 1). Furthermore, using the volume data collected by three-dimensional scanning of the ablation site and its surrounding area, the movement direction and the amount of movement of the ablation site accompanying respiratory movement are detected, and the ablation position by high-intensity ultrasound is based on these detection results. There has also been proposed a method for improving the irradiation accuracy and irradiation efficiency of high-intensity ultrasonic waves on the ablation site by automatically correcting for (see, for example, Patent Document 2).
JP 2000-237205 A JP 2006-136441 A

  According to the method described in Patent Document 2 described above, by automatically tracking the ablation site that moves with respiratory movement in the patient's body, the focus of the high-intensity ultrasound is set to the ablation position of the preset ablation site. Since it becomes possible to always make it correspond, the safety | security in ablation treatment can be improved. However, when the automatic tracking of the ablation site accompanied by respiratory movement and the ablation treatment are alternately performed, according to the method described in Patent Document 2, automatic processing is performed based on volume data collected from a wide three-dimensional region in the patient's body. Since calculation processing for tracking is performed, a large calculation time is required. For this reason, when accurate automatic tracking is required, the efficiency of ablation treatment decreases, and in order to increase the efficiency of ablation treatment, the accuracy of automatic tracking must be sacrificed. ing.

  The present invention has been made in view of the above-mentioned problems, and its purpose is to accompany respiratory movement in a patient's body in ablation treatment using high-intensity ultrasound performed under observation of image data. An object of the present invention is to provide an ultrasonic therapy apparatus capable of improving the accuracy and efficiency of cauterization in cauterization treatment by accurately detecting the moving direction and amount of the moving cauterization site in a short time.

  In order to solve the above-described problem, the ultrasonic therapy apparatus according to the first aspect of the present invention is an ultrasonic therapy for performing cauterization treatment by irradiating a patient with a high-power ultrasonic wave while observing image data. In the apparatus, volume data collection means for collecting volume data of a three-dimensional region including the treatment target part, and an ablation part including the treatment target part for the volume data collected in the reference breathing time phase of the patient Ablation site movement area setting means for setting the movement area of the ablation site in one or a plurality of breathing cycles as the ablation site movement area, and the volume data collected in each of a plurality of different respiratory time phases. Ablation part movement detection means for performing a calculation process on the ablation part movement region and detecting movement information of the ablation part; And cauterizing position correcting means for correcting the ablation position in the ablation site based on the information, is characterized by comprising an ultrasonic irradiating means for irradiating a strong ultrasonic waves to corrected the ablation position.

  According to the present invention, in the cauterization treatment using high-intensity ultrasound performed under the observation of image data, the movement direction and the amount of movement of the ablation site that moves with respiratory movement in the patient's body can be accurately determined in a short time. By detecting in this manner, it is possible to improve the ablation accuracy and the ablation efficiency in the ablation treatment.

  Embodiments of the present invention will be described below with reference to the drawings.

  In the embodiment of the present invention described below, 3 consisting of the treatment target region and the margin region around it based on the volume data of the reference respiratory time phase collected from the three-dimensional region in the patient body including the treatment target region such as a tumor. A dimensional ablation site is set, and a movement region in the respiratory movement of the ablation site based on volume data collected in time series in a plurality of respiratory time phases subsequent to the reference respiratory time phase Set as. Next, when irradiating intense ultrasonic waves to a predetermined ablation position of the ablation site according to the ablation plan based on the volume data collected in the reference breathing time phase, two volume data collected in each of the adjacent breathing time phases are obtained. By performing arithmetic processing within the range of the ablation site movement area, the movement information of the ablation site is detected, and intense ultrasound is applied to the ablation position corrected based on the detection result.

  In the following embodiments, volume data based on B-mode data obtained by an ultrasonic probe in which a plurality of vibration elements are two-dimensionally arranged is collected, and respiratory movement of the ablation site is detected using this volume data. However, the present invention is not limited to this. For example, color Doppler data or volume data based on B mode data and color Doppler data may be used. These B mode data and color Doppler data may be contrast media. It may be obtained from the patient to whom is administered.

(Device configuration)
An embodiment of the present invention will be described with reference to FIGS. FIG. 1 is a block diagram showing the overall configuration of the ultrasonic therapy apparatus according to the present embodiment, and FIG. 2 is a block diagram showing a specific configuration of a volume data collection unit provided in the ultrasonic therapy apparatus. .

  In FIG. 1, an ultrasonic therapy apparatus 100 includes a volume data collecting unit 2 that collects three-dimensional data (volume data) by three-dimensional scanning of ultrasonic waves into a patient body, and a concave piezoelectric vibrator 31. Drive to the ultrasonic irradiation unit 3 that irradiates high-power ultrasonic waves to the ablation site (that is, the region to be treated and the margin area around it) and the piezoelectric vibrator 31 provided in the ultrasonic irradiation unit 3 A vibrator driving unit 4 for supplying signals, a three-dimensional image data generating unit 5 for processing volume data supplied from the volume data collecting unit 2 to generate three-dimensional image data, and an MPR set for the volume data An MPR image data generation unit 6 that generates MPR image data in a cross section is provided.

  In addition, the ultrasonic therapy apparatus 100 sets the three-dimensional movement region in the respiratory movement of the ablation site based on the time-series volume data supplied from the volume data collection unit 2. And ablation site movement detection unit 8 for detecting movement information (that is, movement direction and movement amount) of the ablation site based on two volume data collected in each of adjacent respiratory phases, and movement of the ablation site An ablation position correction unit 9 that corrects the ablation position based on the information, a movement mechanism control unit 10 that generates a movement control signal based on the corrected ablation position information, and the ultrasonic irradiation unit 3 according to the movement control signal are predetermined. And a moving mechanism 11 that moves a predetermined distance in the direction of the MPR image data generated by the MPR image data generator 6 and the three-dimensional image data generator 5. Display unit 12 that superimposes and displays information such as ablation site, ablation position or focal position on the generated three-dimensional image data, setting of volume data collection conditions, setting of MPR section, setting of seed point, ablation plan An input unit 13 for inputting various command signals, a biological signal detection unit 14 for detecting a respiratory waveform of the patient and setting a respiratory time phase based on the obtained respiratory waveform data, The system control part 15 which controls each above-mentioned unit with which the ultrasonic treatment apparatus was provided is provided.

  Each unit will be described in more detail. The volume data collection unit 2 shown in FIG. 2 transmits an ultrasonic pulse (transmission ultrasonic wave) to a three-dimensional region in a patient body including a treatment target site, and receives an ultrasonic reflected wave (reception ultrasonic wave) obtained from the patient body. An ultrasonic probe 21 having a plurality of vibration elements that convert an acoustic wave into an electrical signal (received signal), and a drive signal for transmitting an ultrasonic pulse in a predetermined direction in the three-dimensional region. And a transmission / reception unit 22 for phasing and adding reception signals of a plurality of channels obtained from these oscillating elements, and a reception signal for processing the received signals after phasing and adding to generate B-mode data. A processing unit 23 and a volume data generation unit 2 that generates volume data by arranging the above-described B-mode data obtained by three-dimensional scanning of the patient's body in correspondence with the transmission / reception direction of the ultrasonic waves. It is equipped with a.

  The ultrasonic probe 21 has N vibrating elements (not shown) that are two-dimensionally arranged at the tip thereof, and each of these vibrating elements is connected to an input / output terminal of the transmitting / receiving unit 22 via an N-channel multicore cable. It is connected. The vibration element is an electroacoustic transducer, which converts an electric pulse (drive signal) into an ultrasonic pulse (transmitted ultrasonic wave) at the time of transmission, and converts an ultrasonic reflected wave (received ultrasonic wave) into an electric reception signal at the time of reception. It has the function to convert to. The ultrasonic probe 21 has a sector scan support, a linear scan support, a convex scan support, and the like, and the operator can arbitrarily select according to the diagnostic part. A case in which an ultrasonic probe for sector scanning in which the vibration elements are two-dimensionally arranged will be described.

  Next, the transmission / reception unit 22 transmits a drive signal for radiating transmission ultrasonic waves to the body of the patient to N vibration elements provided in the ultrasonic probe 21, and the vibration elements Is provided with a receiving unit 222 that performs phasing addition on the N-channel received signal obtained from the above.

  The transmission unit 221 includes a rate pulse generator 223, a transmission delay circuit 224, and a drive circuit 225. The rate pulse generator 223 repeats transmission ultrasonic waves by dividing the reference signal supplied from the system control unit 15. A rate pulse that determines the period is generated. The transmission delay circuit 224 is composed of N-channel independent delay circuits, and has a delay time (focusing delay time) for focusing the transmission ultrasonic wave to a predetermined depth in order to obtain a narrow beam width in transmission, and a predetermined delay time. A delay time (deflection delay time) for radiating transmission ultrasonic waves in the transmission / reception direction (θpx, φqy) is given to the rate pulse. Then, the N-channel independent drive circuit 225 generates a drive pulse for driving the N vibration elements incorporated in the ultrasonic probe 21 based on the rate pulse.

  On the other hand, the reception unit 222 includes a preamplifier 226 composed of N channels, an A / D converter 227, a reception delay circuit 228, and an adder 229. The preamplifier 226 amplifies a minute reception signal converted into an electric signal by the above-described vibration element to secure a sufficient S / N. The N-channel reception signal amplified by the preamplifier 226 is converted into an A / D converter. In 227, the digital signal is converted. The reception delay circuit 228 has a delay time for converging an ultrasonic reflected wave from a predetermined depth and a deflection delay for setting a strong reception directivity for a predetermined transmission / reception direction (θpx, φqy). Time is given to each of the N-channel reception signals output from the A / D converter 227, and the adder 229 adds and combines the reception signals supplied from these reception delay circuits 228. That is, the reception delay circuit 228 and the adder 229 perform phasing addition (addition after phase matching) for the reception signal obtained from a predetermined direction.

  FIG. 3 shows the relationship of ultrasonic transmission / reception directions (θpx, φqy) with respect to orthogonal coordinates (Xo-Yo-Zo) with the central axis of the ultrasonic probe 21 as the Zo axis. For example, N vibrating elements are two-dimensionally arranged in the Xo-axis direction and the Yo-axis direction, and θpx and φqy indicate transmission / reception directions projected on the Xo-Zo plane and the Yo-Zo plane.

  Next, the reception signal processing unit 23 illustrated in FIG. 2 includes an envelope detector 231 that performs envelope detection on the reception signal after the phasing addition supplied from the adder 229 of the reception unit 222, and an envelope detection after the envelope detection A logarithmic converter 232 for logarithmically converting the received signal to generate B-mode data is provided. However, the envelope detector 231 and the logarithmic converter 232 may be configured by changing the order.

  As shown in FIG. 2, the volume data generation unit 24 includes an ultrasonic data storage unit 241, an interpolation processing unit 242, and a volume data storage unit 243. The ultrasonic data storage unit 241 is obtained by three-dimensional scanning of the patient. The B-mode data generated by the reception signal processing unit 23 based on the received signal is supplied from the biological signal detection unit 14 via the ultrasonic transmission / reception direction information supplied from the system control unit 15 or the system control unit 15. Respiratory phase information is sequentially stored as supplementary information.

  On the other hand, the interpolation processing unit 242 forms three-dimensional ultrasound data by arranging a plurality of B-mode data in the predetermined breathing time phase read from the ultrasound data storage unit 241 in correspondence with the ultrasound transmission / reception direction, and further Then, volume data composed of isotropic voxels is generated by interpolating unequally spaced voxels constituting the three-dimensional ultrasound data. The obtained volume data is temporarily stored in the volume data storage unit 243 using the information on the respiratory phase as supplementary information.

  Returning to FIG. 1, the ultrasonic irradiation unit 3 includes a piezoelectric vibrator 31 that is filled with, for example, a coupling liquid 32 made of degassed water and emits strong ultrasonic waves at an upper part thereof. The tip of the ultrasonic probe 21 is swingably mounted in a hole provided in a substantially central portion of the piezoelectric vibrator 31.

  On the other hand, a coupling film 33 made of a polymer material having an acoustic impedance substantially equal to that of the coupling liquid 32 is provided at the contact portion of the ultrasonic irradiation unit 3 with the patient body surface, and is emitted from the piezoelectric vibrator 31. The powerful ultrasonic wave for treatment and the ultrasonic wave for imaging transmitted / received by the ultrasonic probe 21 are efficiently transmitted to the patient's body through the coupling film 33 and the coupling liquid 32 having substantially the same acoustic characteristics as the patient tissue. Sent and received.

  Note that one or a plurality of concave piezo elements are used as the piezoelectric vibrator 31, and a drive signal is supplied to the piezo elements on the first surface (convex surface) and the second surface (concave surface). Electrodes for mounting are respectively mounted. The convex electrode is fixed to a support base (backing material), and the concave electrode is an acoustic matching layer and a protective film (both not shown) for efficiently irradiating the patient with intense ultrasonic waves. Covered by.

  Next, the vibrator drive unit 4 has a function of supplying a drive signal to the piezoelectric vibrator 31 in order to radiate strong ultrasonic waves into the patient's body, and has a center frequency substantially equal to the resonance frequency of the piezoelectric vibrator 31. In order to efficiently supply the burst wave output from the burst wave generator 41 that generates the burst wave, the power amplifier 42 that amplifies the burst wave to a predetermined amplitude, and the burst wave output from the power amplifier 42 to the piezoelectric vibrator 31 A matching circuit 43 that performs impedance matching is provided.

  On the other hand, the three-dimensional image data generation unit 5 includes an opacity / color tone setting unit (not shown) and a rendering processing unit. The opacity / color tone setting unit reads the volume data in the predetermined breathing time phase of the patient once stored in the volume data storage unit 243 in the volume data generation unit 24 of the volume data collection unit 2, and voxels of these volume data Set the opacity and tone based on the value. On the other hand, the rendering processing unit processes the volume data based on the opacity and color tone information set by the opacity / color tone setting unit, and generates three-dimensional image data such as volume rendering image data.

  The MPR image data generation unit 6 reads the volume data of the reference respiratory time phase stored in the volume data storage unit 243 of the volume data generation unit 24 and supplies the volume data from the input unit 13 when setting the ablation site movement region described later. Based on the MPR cross-section setting information, MPR image data used for setting the seed point is generated.

  Furthermore, volume data sequentially supplied from the volume data generation unit 24 is received when confirming the focal position with respect to the ablation position before ablation, monitoring of ablation site during ablation, and confirming the ablation effect at the ablation site after ablation. Then, time-series MPR image data is generated by extracting voxels of the volume data corresponding to a preset MPR section.

  On the other hand, the ablation site movement area setting unit 7 sets the ablation site based on the seed point setting information set by the input unit 13 for the treatment target site of the MPR image data in the reference respiratory time phase displayed on the display unit 12. Further, the movement range in the respiratory movement of the ablation site is set as the ablation site movement region. As a reference breathing time phase for generating MPR image data for the purpose of setting a seed point, an expiratory time phase with relatively little respiratory movement in the patient is usually selected. Details of the respiratory time phase including phases will be described later.

  Next, a method for setting the ablation site movement region by the MPR image data generation unit 6, the ablation site movement region setting unit 7 and the input unit 13 will be described with reference to FIG. The treatment target part 51a and the treatment target part 51b shown in FIG. 4 are treatment target parts in the volume data of the expiration time phase and the inspiration time phase, and the expiration time phase (reference breathing time phase) existing at the position of the treatment target part 51a. The treatment target part is schematically moved to the position of the treatment target part 51a in the expiration time phase after sequentially moving toward the position of the treatment target part 51b in the inspiration time phase with respiratory movement in the patient's body. It shows.

  When setting the ablation site movement region, the MPR image data generation unit 6 is based on the MPR cross section set by the MPR cross section setting unit 131 of the input unit 13 with respect to the volume data of the reference respiratory time phase including the treatment target site of the patient. MPR image data is generated, and the seed point setting unit 132 of the input unit 13 sets a seed point in the vicinity of the center of the treatment target site in the MPR image data displayed on the display unit 12.

  Next, the calculation unit (not shown) of the ablation site movement region setting unit 7 collects the region growing method starting from the set seed point at the reference breathing time phase (first breathing time phase). The contour of the treatment target part 51a is extracted by applying to the volume data, and a predetermined amount of margin is added to the extracted outline to set the ablation part 52a in the reference breathing time phase.

  Next, the calculation unit calculates the center of gravity of the ablation site 52a, and the volume collected in the second breathing time phase following the reference breathing time phase with the region expansion method using the obtained center of gravity as a new seed point. Apply to data. Then, the contour of the treatment target part in the volume data is extracted, and a predetermined amount of margin is added to the extracted outline to set the ablation part in the second respiratory time phase.

  Collected in each of a reference respiratory time phase and a plurality of respiratory time phases (second respiratory time phase, third respiratory time phase, fourth respiratory time phase,... Following this reference respiratory time phase. The seed point setting method for the volume data will be described with reference to Fig. 5. As described above, the calculation unit of the ablation site movement region setting unit 7 is an input unit for the treatment target site of the MPR image data in the reference respiratory time phase. The ablation site 521 (ablation site 52a in FIG. 4) in the volume data of the reference respiratory phase is set by the region expansion method starting from the seed point S1 set by the 13 seed point setting unit 132, and further, the ablation site 521 of the ablation site 521 is set. The center of gravity W1 is calculated.

  Next, the ablation site 522 in the volume data of the second respiratory phase is set by the region expansion method using the center of gravity W1 as the seed point S2, and the center of gravity W2 of the ablation site 522 is calculated. In the same manner, the setting of the ablation parts 523, 524,... And the calculation of the center of gravity W3, W4,... In the volume data of the third respiratory time phase, the fourth respiratory time phase,. Do.

  When the setting of the ablation site is completed for the volume data collected in each respiratory time phase from the expiration time phase (reference breathing time phase) through the inspiration time phase to the expiration time phase again, The ablation site moving area 53 shown in FIG. 4 is set by synthesizing the ablation site set in the time phase (that is, taking the logical sum of the ablation sites).

  Next, the ablation site movement detection unit 8 of FIG. 1 has an arithmetic circuit (not shown), and adjacent respiratory time phases in time-series volume data newly collected by three-dimensional scanning with respect to the ablation site movement region. The movement information (movement direction and movement amount) of the ablation site is detected by comparing the two volume data in. Various methods for detecting movement of image data have already been proposed. Here, the difference value between voxels is calculated while sequentially shifting two volume data in adjacent respiratory time phases in three-dimensional directions. The movement information of the ablation site in the volume data is detected on the basis of the shift direction and the shift amount in which the absolute value sum or square sum of the difference values is minimized.

The above-described method (hereinafter referred to as “minimum difference sum method”) will be described in more detail with reference to FIG. In FIG. 6, the signal intensity (luminance) of the voxel (p, q, r) in the volume data of the m-th breathing time phase is A (p, q, r), following (adjacent) the m-th breathing time phase. If the signal intensity of the voxel (p, q, r) in the volume data of the (m + 1) th respiratory time phase is B (p, q, r), the evaluation function β _AB (j , K, s) can be obtained by the following equation (1).

The volume function data of the (m + 1) th respiratory time phase is sequentially moved in the p direction, the q direction, and the r direction with respect to the volume data of the mth respiratory time phase, and the evaluation function β _AB (j, k, s) is calculated. When β _AB (j, k, s) has a minimum value at j = jx, k = kx and s = sx, the ablation site in the volume data of the (m + 1) th respiratory phase is It is detected that the ablation site in the volume data of the breathing phase of m has moved by jx voxels in the p direction, kx voxels in the q direction, and sx voxels in the r direction. In the above equation (1), Na is the product of the number of voxels P in the p direction, the number of voxels Q in the q direction, and the number of voxels R in the r direction used to calculate the evaluation function β _AB (j, k, s). is there.

  Returning to FIG. 1 again, the ablation position correction unit 9 corrects the ablation position of the ablation site set in advance in the ablation plan based on the movement information of the ablation site detected by the ablation site movement detection unit 8 and moves the ablation position. The mechanism control unit 10 performs movement control for correcting the focal position of the strong ultrasonic wave in the ultrasonic irradiation unit 3 based on the corrected ablation position information supplied from the ablation position correction unit 9 via the system control unit 15. Generate a signal. And the movement mechanism part 11 correct | amends the focus position of the ultrasonic irradiation part 3 according to the movement control signal supplied from the movement mechanism control part 10, and the said ablation position of the ablation site which moved with the respiratory movement in a patient body A strong ultrasonic wave is irradiated to the.

  On the other hand, the display unit 12 includes the ablation site and the ablation site movement region set by the ablation site movement area setting unit 7, the focal position of the strong ultrasonic wave by the ultrasonic irradiation unit 3, information about the ablation site during or after cauterization, and the like. A display data generation circuit (not shown) having a function of superimposing and displaying the MPR image data generated by the MPR image data generation unit 6 or the 3D image data generated by the 3D image data generation unit 5. A conversion circuit and a monitor are provided. The display data generation circuit generates display data by superimposing the above-described various information and patient information on MPR image data or three-dimensional image data, and the conversion circuit performs D / A conversion and television on the display data. The format is converted and displayed on the monitor.

  The input unit 13 is an interactive interface provided with an input device such as a display panel such as a touch command screen on the operation panel, a keyboard, a switch, a selection button, and a mouse, and volume data collected by three-dimensional scanning of the patient. An MPR cross-section setting unit 131 that sets one or a plurality of MPR cross-sections, a seed point setting unit 132 that sets a seed point for a treatment target site in MPR image data generated by these MPR cross-sections, An ablation plan setting unit 133 is provided for setting an ablation plan for the ablation site of the volume data collected in the reference breathing time phase. Further, setting of volume data collection conditions, setting of display conditions for MPR image data and 3D image data, input of various command signals, and the like are performed using the above-described input device and display panel provided in the input unit 13.

  Next, a specific example of the ablation plan set by the ablation plan setting unit 133 of the input unit 13 will be described with reference to FIG. However, in FIG. 7, for easy understanding, the ablation site set based on the MPR image data of the reference respiratory time phase and a plurality of ablation positions set for the ablation site are two-dimensionally shown. However, the actual setting is performed three-dimensionally. FIG. 7A shows three-dimensional image data 71 generated by the three-dimensional image data generation unit 5 based on volume data obtained by three-dimensional sector scanning using the ultrasonic probe 21 of the volume data collection unit 2. A three-dimensional region of interest 73 is set by the ablation plan setting unit 133 of the input unit 13 so as to surround the ablation site 72 of the three-dimensional image data 71. Then, the set position information of the region of interest 73 is stored in its own storage circuit (not shown).

  Next, the ablation plan setting unit 133 divides the region of interest 73 into small cubic regions corresponding to the focused ultrasonic beam width, and further calculates the center coordinates of these cubic regions to set the ablation position. For example, FIG. 7B shows the ablation positions C1 to C6, C7 to C13,... Set by the ablation plan setting unit 133. Usually, since the ablation site 72 is larger than the focused beam width of the intense ultrasound, the entire region of the ablation site 72 is moved by sequentially moving the focal point of the intense ultrasound to a plurality of ablation positions preset in the ablation site in the ablation plan. Shochu is performed against.

  In this case, as shown in FIG. 7C, the focal point of the powerful ultrasonic wave is preferably moved in the direction indicated by the arrow with the deep cauterization position C1 as the starting point, but is not limited to this method. Alternatively, it may be performed discretely. However, since the ultrasonic transmissivity is remarkably deteriorated in the region once cauterized and caused by heat-denatured necrosis, it is desirable to prioritize cauterization in the deep region over cauterization in the shallow region. Each of the cubic regions in the region of interest 73 shown in FIG. 7 (c) corresponds to FIG. 7 (b), and reference numerals such as ablation positions C1, C2,. Yes.

  Next, FIG. 8 shows a specific example of MPR image data displayed on the display unit 12 when ablation treatment is performed on the ablation site based on the ablation plan. FIG. 8 shows three MPR sections Pm1 to Pm3 preset for volume data Vb including the ablation site Tm, and MPR image data Mp1 to Mp3 generated in each of these MPR sections Pm1 to Pm3. In general, each of the MPR cross sections Pm1 to Pm3 is set to be orthogonal to each other, and the intersection point thereof substantially coincides with the center of the ablation site Tm. For example, MPR image data MP1 and MPR image data generated in the MPR section Pm1 including the central axis Zo of the ultrasonic probe 21 shown in FIG. 3 and parallel to the Xo-Zo plane and the MPR section Pm2 parallel to the Yo-Zo plane. The MPR image data Mp3 generated in the MPR section Pm3 perpendicular to Mp2 and the central axis Zo is displayed on the monitor of the display unit 12.

  In this case, since the cauterized tissue is displayed with high brightness below the cauterization site, it is possible to easily grasp the presence or absence of cauterization leakage and the cauterization state. Also, the cauterized area and the non-cauterized area may be displayed graphically using different brightness and colors. According to this display method, the ablation scheduled area and the ablated area can be clearly distinguished and displayed, so that the progress of the ablation treatment can be easily grasped.

  Returning to FIG. 1, the biological signal detection unit 14 includes a respiration sensor that detects a respiration waveform of the patient and a respiration time phase setting unit that sets a respiration time phase based on the respiration waveform detected by the respiration sensor. (Not shown).

  FIG. 9 shows a respiratory waveform 81 for four periods detected from the patient and a respiratory time phase set based on the respiratory waveform 81. Here, for the sake of convenience, as shown in FIG. 9A, the period from the time phase t1x, t2x, t3x,... Where the respiration waveform 91 is minimized to the time phase t1y, t2y, t3y,. Is the inhalation period Te, the time phase t1y, t2y, t3y,... To the time phase t2x, t3x, t4x,... Is the expiration period Tb, and the time phases t1y, t2y, t3y,. The end phase of the expiration period Tb in which the change in the time phase and the respiratory waveform 81 is relatively small or the vicinity thereof is defined as the expiration time phase. As described above, the three-dimensional image data used for setting the ablation plan and the MPR image data used for setting the ablation site are the volume data collected using the above-mentioned expiration time phase as the reference breathing time phase. Based on.

  And the said respiratory time phase setting part with which the above-mentioned biological signal detection part 14 was equipped performs the differential process of the respiration waveform 81, for example, produces a trigger pulse as shown in FIG.9 (b) at the time phases t1x, t2x, t3x. ,..., And expiration time phases t11, t21, t31,... That have passed a predetermined time τ0 from these trigger pulses are set as reference breathing time phases. Further, the respiratory time phase setting unit sets time phases t12 to t1M at predetermined time intervals (for example, 50 msec) based on the reference respiratory time phase t11, and time phases at predetermined time intervals based on the reference respiratory time phase t21. t22 to t2M and time phases t32 to t3M... at predetermined time intervals with reference to the reference respiratory time phase t31 are set as time phases for detecting movement information of the ablation site.

  Next, the system control unit 15 includes a CPU and a storage circuit (not shown), and the above-described various information input or set by each unit of the input unit 13 is stored in the storage circuit. Then, the CPU controls each unit of the ultrasonic therapy apparatus 100 based on the above-described input information and setting information, and detects the movement of the ablation site that moves along with the respiratory movement in the patient and the detection result. The focus position correction of the powerful ultrasonic wave based on is performed.

(Cauterization procedure of the ablation site)
Next, the cauterization procedure of the cauterization site in the present embodiment will be described along the flowchart of FIG.

  Prior to ablation treatment for the patient, the operator of the ultrasonic therapy apparatus 100 inputs patient information at the input unit 13, then sets volume data collection conditions, sets three-dimensional image data generation conditions, and further MPR image data. And setting display conditions for 3D image data. These input information and setting information are stored in the storage circuit of the system control unit 15.

  Next, the ultrasonic irradiation unit 3 is arranged on the surface of the patient body that seems to be suitable for irradiation of intense ultrasonic waves to the treatment target site. In this case, the volume data collection unit 2, the three-dimensional image data generation unit 5, and the display unit 12 are set in an operating state in advance, and the ultrasonic irradiation unit 3 is observed under the observation of the three-dimensional image data generated by these units. Is arranged at a suitable position (step S1 in FIG. 10).

  When the above-described initial setting is completed, the operator inputs a command signal for starting the setting of the cauterization site movement region at the input unit 13, and the command signal is supplied to the system control unit 15. Setting of the ablation site movement area is started (step S2 in FIG. 10).

  When collecting volume data necessary for setting the ablation site movement area, the rate pulse generator 223 in the transmission / reception unit 22 of the volume data collection unit 2 divides the reference signal supplied from the system control unit 15 to generate a rate pulse. Generated and supplied to the transmission delay circuit 224. The transmission delay circuit 224 uses, as the rate pulse, a focusing delay time for focusing the ultrasonic wave to a predetermined depth and a deflection delay time for transmitting the ultrasonic wave in the first transmission / reception direction (θ1, φ1). The rate pulse is supplied to the N-channel driving circuit 225. Next, the drive circuit 225 generates a drive signal based on the rate pulse supplied from the transmission delay circuit 224, supplies this drive signal to the N vibrating elements in the ultrasonic probe 21, and sends the ultrasonic pulse into the patient's body. Radiate.

  A part of the radiated ultrasonic pulse is reflected by an organ boundary surface or tissue having different acoustic impedance, is received by the same vibration element at the time of transmission, and is converted into an N-channel electrical reception signal. Next, these received signals are amplified by the preamplifier 226 and then converted into digital signals by the A / D converter 227. Further, the received delay circuit 228 focuses received ultrasonic waves from a predetermined depth. The delay time for focusing and the delay time for deflection for setting a strong reception directivity with respect to the received ultrasonic wave from the transmission / reception direction (θ1, φ1) are given and then phased and added by the adder 229.

  Then, the envelope detector 231 and the logarithmic converter 232 of the reception signal processing unit 23 to which the reception signal after the phasing addition is supplied perform envelope detection and logarithmic conversion on the reception signal to obtain B-mode data. The transmission / reception direction is stored as supplementary information in the ultrasonic data storage unit 241 of the volume data generation unit 24.

  When the generation and storage of the B-mode data in the transmission / reception direction (θ1, φ1) is completed, the system control unit 15 controls the delay times in the transmission delay circuit 224 and the reception delay circuit 228 of the transmission / reception unit 22 in the θpx direction. Transmission / reception direction (θpx, φqy) (θpx = θ1 + (px−1) Δθ (px = 2−Px), φqy = φ1 + (qy−1) Δφ (qy = 2−2) sequentially updated by Δφ in Δθ and φqy directions. Qy)) is subjected to three-dimensional scanning by transmitting and receiving ultrasonic waves in the same procedure. The B-mode data obtained in each transmission / reception direction is also stored in the ultrasonic data storage unit 241 with the transmission / reception direction as supplementary information.

  On the other hand, the interpolation processing unit 242 of the volume data generation unit 24 forms three-dimensional ultrasonic data by arranging a plurality of B-mode data read from the ultrasonic data storage unit 241 in correspondence with the ultrasonic transmission / reception direction, Furthermore, volume data composed of isotropic voxels is generated by interpolating unequally spaced voxels constituting the three-dimensional ultrasound data. Then, the obtained volume data is temporarily stored in the volume data storage unit 243 using the respiratory time phase information as supplementary information (step S3 in FIG. 10). By repeating such a procedure for the reference breathing time phase and each of a plurality of breathing time phases subsequent to the reference breathing time phase, the volume data storage unit 243 stores the time series collected in these breathing time phases. Volume data is stored with respiratory phase information.

  Next, the MPR image data generation unit 6 reads the volume data of the reference respiratory time phase (expiration time phase) stored in the volume data storage unit 243 of the volume data generation unit 24. Then, MPR image data is generated based on the MPR slice setting information supplied from the MPR slice setting unit 131 of the input unit 13 via the system control unit 15, and the obtained MPR image data is displayed on the monitor of the display unit 12. indicate. (Step S4 in FIG. 10).

  Next, the operator uses the seed point setting unit 132 of the input unit 13 to set a seed point near the center of the treatment target site in the MPR image data displayed on the display unit 12 (step S5 in FIG. 10). Then, the seed point setting information is supplied to the ablation site movement region setting unit 7 via the system control unit 15.

  On the other hand, the ablation site movement region setting unit 7 applies the region expansion method starting from the seed point set by the seed point setting unit 132 of the input unit 13 to the volume data of the reference breathing phase, and outlines the treatment target region. Is extracted, and a predetermined amount of margin is added to the extracted contour to set the ablation site in the reference breathing time phase.

  Further, the ablation site movement region setting unit 7 calculates the center of gravity of the set ablation site, and the second breathing time phase following the reference breathing time phase with the region expansion method using the obtained center of gravity as a new seed point. The ablation site in this breathing phase is set by applying to the volume data. By repeating the same procedure, the ablation site in the volume data of the third respiratory time phase, the fourth respiratory time phase, the fifth respiratory time phase,... Is set (step S6 in FIG. 10). Then, the ablation site movement region is set by synthesizing a plurality of ablation sites set in each breathing time phase from the reference breathing time phase (expiration time phase) through the inspiration time phase to the expiration time phase again ( Step S7 in FIG.

  On the other hand, the 3D image data generation unit 5 processes the volume data in the reference breathing time phase of the patient read from the volume data storage unit 243 to generate 3D image data, and the display unit 12 displays the 3D image data. The three-dimensional image data of the reference respiration time phase supplied from the generation unit 5 and the ablation site information of the reference respiration time phase supplied from the ablation site movement area setting unit 7 are synthesized and displayed on the own monitor (FIG. 10). Step S8).

  An operator observing the three-dimensional image data displayed on the display unit 12 uses the ablation plan setting unit 133 of the input unit 13, and a plurality of ablation positions with respect to the ablation site of the three-dimensional image data and the ablation positions thereof. An ablation order is set (step S9 in FIG. 10).

  When the setting of the ablation site movement area and the setting of the ablation plan are completed, the operator inputs a command signal for starting ablation for the ablation site at the input unit 13, and this command signal is supplied to the system control unit 15. As a result, ablation treatment for the patient is started (step S10 in FIG. 10).

  During the cauterization treatment, the movement mechanism control unit 10 controls the movement control unit 11 based on the instruction signal supplied from the system control unit 15, and the reference breathing time phase (first breathing time phase) set in the cauterization plan. The ultrasonic irradiation unit 3 is moved so that the focal point of the strong ultrasonic wave coincides with the first ablation position (first ablation position). Next, the system control unit 15 controls the vibrator driving unit 4 to irradiate the first cauterization position with intense ultrasonic waves.

  Next, the volume data collection unit 2 performs three-dimensional scanning on the ablation site movement area set by the ablation site movement area setting unit 7 according to the same procedure as in step S3 described above, Volume data in the second respiratory time phase is collected (step S11 in FIG. 10).

  On the other hand, the ablation site movement detection unit 8 compares the volume data of the reference breathing time phase supplied from the volume data collection unit 2 with the volume data of the second breathing time phase within the range of the ablation site movement region. The movement information of the ablation site in the volume data is detected (step S12 in FIG. 10).

  Next, the ablation position correction unit 9 preliminarily performs the ablation plan using the volume data of the reference respiratory time phase based on the movement information of the ablation site in the second respiratory time phase detected by the ablation site movement detection unit 8. The set first cauterization position is corrected (step S13 in FIG. 10). And the movement mechanism control part 10 produces | generates a movement control signal based on the 1st ablation position after the correction | amendment in the 2nd respiration time phase supplied from the ablation position correction | amendment part 9 via the system control part 15, The moving mechanism unit 11 updates the position and direction of the ultrasonic irradiation unit 3 according to the movement control signal supplied from the moving mechanism control unit 10 and is strong against the first ablation position corrected in the second respiratory time phase. Ultrasonic waves are irradiated (step S14 in FIG. 10).

  On the other hand, the MPR image data generation unit 6 receives the volume data collected by the three-dimensional scanning for the ablation site during the ablation from the volume data generation unit 24, and extracts the voxel of the volume data corresponding to the preset MPR section. Thus, MPR image data is generated. Next, the display unit 12 superimposes the information on the focal position and the ablation site of the powerful ultrasonic wave on the MPR image data and displays the information on its own monitor. The operator then displays the MPR image on which the information such as the focal position is superimposed and displayed. The ablation position, the ablation effect, etc. are confirmed from the data (step S15 in FIG. 10).

  If intense ultrasound is applied to the first ablation position corrected in the second breathing time phase by the procedure described above for a predetermined time, the third breathing time phase, the fourth breathing time phase, and so on. The movement information is also detected by the same procedure for the ablation site of the volume data in the phase,..., And the intense ultrasonic wave is irradiated to the first ablation position corrected based on the detection result (FIG. 10). Steps S11 to S15). Then, when the cauterization for the first cauterization position is completed, the moving mechanism control unit 10 controls the moving mechanism unit 11 based on the instruction signal from the system control unit 15 to set a reference set in advance in the cauterization plan. Intense ultrasonic waves are applied to the second ablation position in the respiratory phase. Then, cauterization is performed by the same procedure as described above for the second ablation position corrected in the second respiratory time phase, the third respiratory time phase,..., And further, the third ablation position, By performing cauterization in the same procedure for the ablation positions of..., Cauterization treatment is performed for all regions of the ablation site set in the ablation plan (step S16 in FIG. 10).

  According to the embodiment of the present invention described above, the movement information of the ablation site that moves along with the respiratory movement or the like in the patient body is detected, and the focal position of the powerful ultrasonic wave is corrected based on the detection result. When ablation treatment is performed on the ablation site, an area where the ablation site moves within the respiratory cycle is set in advance as an ablation site movement area, and movement information of the ablation site is detected based on volume data in the ablation site movement area. Therefore, accurate movement information can be detected in a short time. For this reason, the ablation accuracy and ablation efficiency for the treatment target site are improved, and further, safety for surrounding normal tissues is ensured.

  That is, according to the present embodiment, tumor cells and the like can be brought into a complete necrotic state by efficient cauterization of the ablation site, so that the possibility of recurrence can be significantly reduced. In addition, it is possible to suppress irradiation damage to normal tissue around the ablation site, and further, the time required for the ablation treatment is shortened, so that the burden on the patient and the operator is reduced and the treatment throughput is improved.

  Further, according to the above-described embodiment, the expiration time phase with relatively little respiratory movement is set as the reference breathing time phase, and the volume data collected in the reference breathing time phase is used as a reference for the ablation site in each time phase. Since the movement information is sequentially detected, the accumulated error generated in the detection result can be reduced, and accordingly, the focal position of the powerful ultrasonic wave can be accurately corrected.

  Furthermore, since the three-dimensional movement information of the ablation site in each respiratory time phase is detected based on the volume data collected from the patient, high detection accuracy can be obtained.

  As mentioned above, although the Example of this invention has been described, this invention is not limited to the above-mentioned Example, It can change and implement. For example, in the above-described embodiment, the case where the movement information of the ablation site is detected based on the volume data collected by the three-dimensional ultrasonic scanning for the patient has been described. However, other examples such as an X-ray CT apparatus and an MRI apparatus are described. The movement information of the ablation site may be detected using the volume data collected by the diagnostic imaging apparatus.

  Further, in the case of collecting volume data by ultrasonic three-dimensional scanning, a case has been described in which volume data is collected based on B-mode data obtained by the ultrasonic probe 21 in which a plurality of vibration elements are two-dimensionally arranged. For example, color Doppler data, or volume data based on B-mode data and color Doppler data may be used, and these B-mode data and color Doppler data may be related to the contrast medium administered. It may be obtained from a patient. Further, the volume data may be collected by mechanically moving an ultrasonic probe in which a plurality of vibration elements are arranged one-dimensionally.

  On the other hand, in the above-described embodiment, the contour of the treatment target region is extracted by the region expansion method starting from the seed point set in the volume data of the reference respiratory time phase, and the ablation site is set based on this contour. As described above, even if the outline of the treatment target part and the outline of the ablation part obtained at this time are approximated by a sphere or a spheroid, the ablation part movement region is set based on the ablation part formed by these shapes. Good.

  In addition, a difference value between voxels is obtained while sequentially shifting two volume data in adjacent respiratory time phases in three-dimensional directions, and a shift direction in which the absolute value sum or the square sum of the difference values is minimized and Although the method of detecting the movement information of the ablation site in the volume data based on the shift amount (minimum difference sum method) has been described, the movement information of the ablation site is detected using other methods such as cross-correlation method and entropy method. May be.

  Furthermore, in the above-described embodiment, as shown in FIG. 5, the case where the center of gravity of the ablation site in the preceding breathing phase is set as the seed point in the subsequent breathing phase has been described. If it is smaller than the size of the part, the seed point set in the volume data of the reference breathing time phase or a seed point newly set in the periphery thereof may be used as the seed point in each subsequent breathing time phase. Absent.

  In the above-described embodiment, the case where the ablation position, the ablation effect, and the like are confirmed by superimposing and displaying the focal position information of intense ultrasonic waves on the MPR image data generated by the MPR image data generation unit 6 is described. However, the above-described information may be superimposed and displayed on the 3D image data generated by the 3D image data generation unit 5.

  In the above-described embodiment, for the sake of simplicity of explanation, the case where the ablation part movement region is set and the detection of the ablation part movement information is described using two volume data collected in adjacent respiratory time phases. However, the present invention is not limited to this, and it is possible to set the ablation site movement region and detect the ablation site movement information by using the volume data collected in different respiratory phases.

1 is a block diagram showing the overall configuration of an ultrasonic therapy apparatus according to an embodiment of the present invention. The block diagram which shows the specific structure of the volume data collection part with which the ultrasonic therapy apparatus of the Example is provided. The figure which shows the relationship between the coordinate of an ultrasonic probe with which the volume data collection part of the Example is provided, and a transmission / reception direction. The figure for demonstrating the setting method of the cauterization site | part movement area | region in the Example. The figure for demonstrating the setting method of the seed point with respect to the volume data of the Example. The figure for demonstrating the detection method of the cauterization site | part movement information in the Example. The figure which shows the specific example of the shochu plan in the Example. The figure which shows the specific example of MPR image data displayed at the time of the cauterization treatment of the Example. The figure which shows the respiration time phase set based on the respiration waveform detected in the biosignal detection part of the Example, and this respiration waveform. The flowchart which shows the cauterization procedure of the cauterization site | part in the Example.

Explanation of symbols

2 ... Volume data collection unit 21 ... Ultrasonic probe 22 ... Transmission / reception unit 23 ... Reception signal processing unit 24 ... Volume data generation unit 3 ... Ultrasonic irradiation unit 31 ... Piezoelectric vibrator 32 ... Coupling liquid 33 ... Coupling film 4 ... Transducer drive unit 41 ... burst wave generator 42 ... power amplifier 43 ... matching circuit 5 ... 3D image data generation unit 6 ... MPR image data generation unit 7 ... ablation site movement area setting unit 8 ... ablation site movement detection unit 9 ... Ablation position correction unit 10 ... movement mechanism control unit 11 ... movement mechanism unit 12 ... display unit 13 ... input unit 131 ... MPR cross-section setting unit 132 ... seed point setting unit 133 ... cauterization plan setting unit 14 ... biological signal detection unit 15 ... system Control unit 100 ... ultrasonic therapy apparatus

Claims (10)

In the ultrasonic therapy device that performs ablation treatment by irradiating the patient's treatment target site with intense ultrasound while observing the image data,
Volume data collection means for collecting volume data of a three-dimensional region including the treatment target part;
An ablation site including the treatment target region is set for the volume data collected in the reference respiratory time phase of the patient, and a movement region of the ablation site in one or a plurality of respiratory cycles is set as an ablation site movement region. Ablation site movement area setting means;
Ablation part movement detection means for performing calculation processing on the ablation part movement region in each of the volume data collected in a plurality of different respiratory time phases and detecting movement information of the ablation part;
Ablation position correcting means for correcting the ablation position in the ablation site based on the movement information of the ablation site;
An ultrasonic treatment apparatus comprising: ultrasonic irradiation means for irradiating the corrected ablation position with intense ultrasonic waves.   Image data generating means for generating image data based on the volume data collected by the volume data collecting means, and seed point setting means for setting a seed point for the treatment site in the image data, The ablation site movement area setting means extracts a contour of the treatment target site by applying a region expansion method starting from the seed point to the volume data collected in the reference respiratory time phase, The ultrasonic therapy apparatus according to claim 1, wherein a margin is added to set the ablation site.   A biological signal detection unit configured to detect a respiratory waveform of the patient and set a plurality of time-series respiratory time phases including an expiration time phase and an inspiration time phase based on the respiratory waveform; The ultrasonic therapy apparatus according to claim 1, wherein the ablation site is set based on the volume data collected with the expiration time phase set by the biological signal detection means as the reference respiratory time phase. .   The ablation site movement detection means applies any one of the minimum difference sum method, the cross-correlation method, or the entropy method to the volume data in the ablation site movement region collected in each of different respiratory time phases, and The ultrasonic therapy apparatus according to claim 1, wherein movement information is detected.   The ablation site movement detecting means selects volume data in the reference respiratory time phase from the volume data collected in time series by the volume data collecting means, and is adjacent to the volume data in the reference respiratory time phase. The ultrasonic therapy apparatus according to claim 1, wherein movement information of the ablation site is sequentially detected using volume data in one respiratory phase.   2. The ultrasonic therapy apparatus according to claim 1, wherein the volume data collection means is an ultrasonic diagnostic apparatus having an ultrasonic probe in which a plurality of vibration elements are two-dimensionally arranged.   The ultrasonic treatment according to claim 6, wherein the volume data collection unit collects the volume data based on at least one of B-mode data and color Doppler data obtained by three-dimensional scanning of the patient. apparatus.   A display means, wherein the display means includes at least one of a focus position of a strong ultrasonic wave, a planned ablation area, and an ablated area on the image data generated by the image data generation means before, during or after ablation. The ultrasonic therapy apparatus according to claim 2, wherein the information is superimposed and displayed.   The ultrasonic therapy apparatus according to claim 2, wherein the image data generation unit generates at least one of three-dimensional image data based on the volume data and MPR image data in a predetermined section of the volume data.   The moving mechanism control means controls movement of the ultrasonic irradiation means, and the moving mechanism control means matches the ablation position of the ablation site corrected by the ablation position correction means with the focal position of the intense ultrasound. The ultrasonic therapy apparatus according to claim 1, wherein the movement of the ultrasonic irradiation means is controlled to do so.

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