JPH09103434A - Ultrasonic treatment device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To improve the safety and certainty of a treatment by receiving the echo of first ultrasonic waves from an ultrasonicwave-for-treatment generation source and the echo of second ultrasonic waves from an ultrasonic probe and constituting the intensity distribution of the ultrasonic waves for the treatment based on reception signals. SOLUTION: The ultrasonic waves for the intensity distribution are cyclically generated from the ultrasonic-wave-for-treatment generation source 2 in a band whose center is a first fundamental frequency and the echo of the ultrasonic waves for the intensity distribution is received by a probe 16 for imaging. The piezo element of the probe 16 for imaging is highly sensitive for both of the first fundamental frequency of the ultrasonic waves for the intensity distribution and the second fundamental frequency of the ultrasonic waves for imaging. Since the intensity distribution is imaged based on lower harmonic components largely included in the echo of the ultrasonic waves for the intensity distribution, the intensity distribution faithful to the actual intensity distribution is obtained and judgement such as the estimation or the like of a heat generation area or the like is highly accurately performed based on the intensity distribution.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

TECHNICAL FIELD The present invention relates to an ultrasonic therapeutic apparatus for focusing an ultrasonic wave to treat an affected area.

[0002]

2. Description of the Related Art Recently, Minimally Invas
The minimally invasive treatment called IVE Treatment (MIT) has been attracting attention, and the ultrasonic treatment apparatus plays a part in this. The ultrasonic treatment device includes a calculus breaking device that focuses ultrasonic waves to crush stones, and a thermotherapy device that focuses ultrasonic waves to heat an affected part such as cancer to cause necrosis.

The piezo method is widely used as a powerful ultrasonic wave generation source for calculus breaking devices. This method has the advantages that the focus can be limited, there are no consumables, intensity control is easy, and the focus position can be changed easily by phase control (delay control) of the drive voltage for multiple piezo elements. (See JP-A-60-145131 and US Pat. No. 4,526,168).

On the other hand, MIT has become one of the keywords in the field of cancer treatment. Especially, in the case of cancer, most of the treatment depends on surgical operation, so that the function and appearance of the organ originally should be considered. In many cases, the morphology is greatly impaired, and even if the life is prolonged, a large burden remains on the patient.
There is a strong demand for the development of a treatment method (apparatus) with less invasion in consideration of L).

In such a trend, hyperthermia therapy has been attracting attention as one of the treatment techniques for malignant neoplasm, so-called cancer. This is a therapeutic method that selectively kills cancer cells only by heating and maintaining the affected area at 42.5 ° C. or higher by utilizing the difference in heat sensitivity between tumor tissue and normal tissue. Here, as a heating method, a method using an electromagnetic wave such as a microwave precedes. However, with this method, it is difficult to selectively heat a deep tumor due to the electrical characteristics of the living body, and good therapeutic results cannot be expected for a tumor having a depth of 5 cm or more. Therefore, a method using ultrasonic energy has been considered for treating a tumor existing at a deep position (Japanese Patent Laid-Open No. 61-13955).
Reference).

[0006] Further, the ultrasonic warming treatment method has been developed into a treatment method in which the ultrasonic waves generated by the piezo element are sharply focused on the affected area to heat the tumor portion to 80 ° C or higher, and the tumor tissue is necrotized instantly. (See US Pat. No. 5,150,711). Unlike the conventional hyperthermia, this treatment method applies ultrasonic waves with extremely high intensity (several hundreds to several thousands W / cm ² ) to a localized area near the focal point (focus point of ultrasonic waves), and It is very important to accurately align the focal point or the action point of the focused ultrasonic wave with the affected area in order to instantly necrotize.

Japanese Patent Laid-Open Nos. 61-13954 and 61-
13956 and JP-A-60-145131 disclose solutions to the above problems. This solution detects the echo from the focal region of the ultrasonic pulse emitted from the therapeutic ultrasonic source by the imaging probe and processes the received signal in the B mode, thereby spatially treating the therapeutic ultrasonic wave. The intensity distribution is obtained.

This solution has the following problems.
The frequency of therapeutic ultrasonic waves is about 1 to 3 MHz, while the frequency of imaging ultrasonic waves is 3.5 MHz or higher. The resonance frequency of the transducer of the imaging probe matches the frequency of ultrasonic waves for imaging. Therefore, even if an echo of a therapeutic ultrasonic wave is received by the imaging probe, its sensitivity is very low, and an accurate intensity distribution cannot be acquired.

Further, according to one method of this solution, the echo of the ultrasonic wave for imaging generated from the probe for imaging and the echo of ultrasonic pulse for intensity distribution are simultaneously received by the imaging probe, and both echoes are received. Process a received signal with mixed components. Therefore, the above solution has a problem that the image contrast cannot be adjusted individually.

Another method of the above solution is to alternately transmit / receive an ultrasonic wave for imaging and transmit / receive an ultrasonic pulse for intensity distribution. according to this,
Although there is an advantage that each image contrast can be adjusted individually, there is a problem that the frame rate becomes low and the real-time property deteriorates.

The above solution also has the following problems. Usually, in ablation treatment by focusing intense ultrasonic waves, the position of the focal region where the ultrasound is focused does not match the actual position of the treatment region due to changes in the acoustic characteristics of the ablation treatment and the like. Therefore, even if the focus is aligned with the object to be treated, there is a problem that the treatment of the object to be treated is incomplete and the healthy part is also adversely affected.

Further, the above solution has the following problems. Ultrasound pulses generated by the therapeutic ultrasound source are reflected near the focal point and the echoes are received by the imaging probe. Imaging ultrasonic waves generated from the imaging probe are reflected in the vicinity of the focal point, and the echoes are received by the imaging probe. In order to match the position of the focal point on the intensity distribution with the position of the focal point on the B-mode tomographic image, the respective generation timings are shifted so that both echoes from the focal point reach the imaging probe at the same time. ing. However, the reception timings of echoes from the same position other than the focus are different because the propagation paths are different. Therefore, there is a problem that spatial inconsistency occurs between the intensity distribution and the B-mode tomographic image.

[0013]

SUMMARY OF THE INVENTION It is an object of the present invention to provide an ultrasonic treatment device which can improve the safety and certainty of treatment.

[0014]

An ultrasonic therapy apparatus according to the present invention comprises a therapeutic ultrasonic wave generation source having a resonance characteristic with respect to a first fundamental frequency, the first fundamental frequency and the second fundamental frequency. And an ultrasonic probe having resonance characteristics, means for driving the therapeutic ultrasonic wave generation source with the drive signal of the first fundamental frequency, and the ultrasonic probe with the drive signal of the second fundamental frequency Driving means, and a receiving means for receiving a first ultrasonic echo from the therapeutic ultrasonic source and a second ultrasonic echo from the ultrasonic probe via the ultrasonic probe. And a configuration unit that configures at least one of an intensity distribution of the therapeutic ultrasonic wave in the subject and a tomographic image in the subject based on a reception signal output from the reception unit.

It further comprises means provided between the receiving means and the constituting means for extracting the echo component of the therapeutic ultrasonic wave and the echo component of the imaging ultrasonic wave from the received signal.

The receiving means includes means for individually amplifying the echo component of the therapeutic ultrasonic wave and the echo component of the imaging ultrasonic wave included in the received signal.

The ultrasonic treatment apparatus according to the present invention comprises a therapeutic ultrasonic wave generation source having resonance characteristics with respect to a first fundamental frequency and a second fundamental frequency, and resonance characteristics with respect to the second fundamental frequency. And an ultrasonic probe having a first driving signal of the first fundamental frequency at the time of treatment, and the second drive signal at the time of intensity distribution imaging by driving the therapeutic ultrasonic wave generation source.
Means for driving the therapeutic ultrasonic wave generation source with a second drive signal having a fundamental frequency, a means for driving the ultrasonic probe with a drive signal having the second fundamental frequency, and the ultrasonic probe during the intensity distribution imaging. The second through the sonic probe
Receiving means for receiving an echo of the therapeutic ultrasonic wave having a spectrum centered on the fundamental frequency and an echo of the imaging ultrasonic wave having a spectrum centering on the second fundamental frequency, and an output of the receiving means. Based on the above, at least one of an intensity distribution of the therapeutic ultrasonic wave in the subject and a tomographic image in the subject is provided.

The energy of the first drive signal is stronger than the energy of the second drive signal.

An ultrasonic therapy apparatus according to the present invention comprises a therapeutic ultrasonic wave generation source having a resonance characteristic for a first fundamental frequency, an ultrasonic probe having a resonance characteristic for a second fundamental frequency, and Means for driving the therapeutic ultrasonic wave generation source with a drive signal of a first fundamental frequency; means for driving the ultrasonic probe with a drive signal of the second fundamental frequency; and the means for driving the ultrasonic probe via the ultrasonic probe. Receiving means for receiving a first ultrasonic echo from the therapeutic ultrasonic generator and a second ultrasonic echo from the ultrasonic probe;
An intensity distribution configuring unit that configures an intensity distribution of the therapeutic ultrasonic wave based on a component of a specific band corresponding to the first fundamental frequency included in the received signal output from the receiving unit; and included in the received signal And a means for forming a tomographic image of the inside of the subject based on the component of the band including the second fundamental frequency.

The specific band is at least one of a low frequency band including the first fundamental frequency and a high frequency band including a frequency that is an integral multiple of the first fundamental frequency.

The intensity distribution constructing means has means for analyzing the spectrum of the received signal and determining the specific band based on the frequency of the highest energy density.

The intensity distribution forming means has an equalizer for correcting the spectrum of the received signal.

The intensity distribution constructing means has means for removing a blood flow component accompanied by a frequency shift from the received signal.

The ultrasonic therapeutic apparatus according to the present invention includes a therapeutic ultrasonic wave generation source, an ultrasonic probe, and the therapeutic ultrasonic wave generation source for generating a first ultrasonic wave from the therapeutic ultrasonic wave generation source. A driving means for driving the source; and an adjusting means for adjusting a driving condition of the driving means based on the echo of the first ultrasonic wave received via the ultrasonic probe.

The adjusting means adjusts at least one of the amplitude of the drive signal input from the drive means to the therapeutic ultrasonic wave generation source and the duration of the drive signal.

The adjusting means adjusts the driving condition of the driving means based on at least one of the amplitude of the echo and the energy corresponding to the specific band.

It further comprises a constituting means for constituting at least one of the intensity distribution and the tomographic image based on the received signal output from the ultrasonic probe.

The apparatus further comprises means for estimating a treatment region based on a region in the intensity distribution that exceeds a predetermined intensity.

It further comprises means for displaying the treatment area by combining it with the tomographic image.

The ultrasonic treatment apparatus according to the present invention includes a therapeutic ultrasonic wave generation source, an ultrasonic probe, and the therapeutic ultrasonic wave generation source for generating a first ultrasonic wave from the therapeutic ultrasonic wave generation source. A first driving means for driving the source, a second driving means for driving the ultrasonic probe to generate ultrasonic waves for imaging from the ultrasonic probe, and the second driving means received through the ultrasonic probe. Means for forming an intensity distribution of the therapeutic ultrasonic wave and a tomographic image in the subject based on the echo of the first ultrasonic wave and the echo of the imaging ultrasonic wave, and an ultrasonic wave based on the shape of the intensity distribution Determining means for determining the presence of the obstacle.

It further comprises means for adjusting the drive condition of the first drive means based on the determination result of the determination means.

It further comprises means for outputting the determination result of the determination means.

The determining means includes means for comparing at least one of the amplitude of the echo of the therapeutic ultrasonic wave and the energy in a predetermined band with a predetermined threshold value.

The ultrasonic therapeutic apparatus according to the present invention comprises a therapeutic ultrasonic wave source, an ultrasonic probe, and the therapeutic ultrasonic wave source for generating therapeutic ultrasonic waves from the therapeutic ultrasonic wave source. Drive means for driving, a receiving means for receiving an echo of the therapeutic ultrasonic wave through the ultrasonic probe, and a harmonic corresponding to a high frequency band including a frequency that is an integral multiple of the fundamental frequency of the therapeutic ultrasonic wave It is provided with means for extracting a component from the output of the receiving means, and means for detecting a focus on which the therapeutic ultrasonic wave is focused based on the harmonic component.

The ultrasonic therapeutic apparatus according to the present invention includes a therapeutic ultrasonic wave source, an ultrasonic probe, and the therapeutic ultrasonic wave generator for generating a therapeutic ultrasonic pulse from the therapeutic ultrasonic wave source. Means for driving a source and for generating ultrasound pulses for imaging from the ultrasound probe,
A means for driving the ultrasonic probe, a receiving means for receiving an echo via the ultrasonic probe, a means for forming a tomographic image in the subject based on the echo, and an intensity of the therapeutic ultrasonic wave are A unit for adjusting the generation timing of the therapeutic ultrasonic pulse is provided so that a noise region generated on the tomographic image by being stronger than the intensity of the imaging ultrasonic pulse appears in a region other than the region of interest.

The ultrasonic therapeutic apparatus according to the present invention comprises a therapeutic ultrasonic wave generating source and a driving means for driving the therapeutic ultrasonic wave generating source to generate the therapeutic ultrasonic wave from the therapeutic ultrasonic wave generating source. And a magnetic resonance diagnostic apparatus that measures a temperature distribution near a focus where the therapeutic ultrasonic waves are focused, and a unit that adjusts a driving condition of the driving unit based on the temperature distribution.

The ultrasonic therapeutic apparatus according to the present invention includes a therapeutic ultrasonic wave generator, an ultrasonic probe, and the therapeutic ultrasonic wave generator for generating a first ultrasonic wave from the therapeutic ultrasonic wave generator. A driving means for driving a source, a constituent means for configuring an intensity distribution of the first ultrasonic wave based on an echo of the first ultrasonic wave received via the ultrasonic probe, and 1
A magnetic resonance diagnostic apparatus that measures a three-dimensional temperature distribution, and an estimation unit that estimates a two-dimensional temperature distribution based on the intensity distribution and the one-dimensional temperature distribution.

The estimating means estimates the two-dimensional temperature distribution based on the total energy of the first ultrasonic waves and the one-dimensional temperature distribution.

The ultrasonic therapeutic apparatus according to the present invention comprises a therapeutic ultrasonic wave generating source, an ultrasonic probe, a synchronizing signal generating means for generating a first synchronizing signal and a second synchronizing signal, and the first synchronizing signal generating means. Means for driving the therapeutic ultrasonic wave generation source according to a synchronization signal, means for driving the ultrasonic probe according to the second synchronization signal, and a time difference between the first synchronization signal and the second synchronization signal. A phase shift means for imparting a phase difference to the echo of the therapeutic ultrasonic wave by changing the time, and a first ultrasonic echo from the therapeutic ultrasonic wave generation source via the ultrasonic probe, Receiving means for receiving an echo of the second ultrasonic wave from the ultrasonic probe; and constituting means for forming an image based on the received signal phase-shifted by the phase-shifting means repeatedly output from the receiving means. Equipped with .

The phase shifting means includes a programmable N-ary counter.

The phase shifting means includes a jitter circuit which outputs the first synchronizing signal in an unstable manner.

The phase shift means increments the time difference at an arbitrary pitch and resets the time difference at a pitch different from the arbitrary pitch.

The ultrasonic therapy apparatus according to the present invention comprises a therapeutic ultrasonic wave source, an ultrasonic probe, and means for driving the therapeutic ultrasonic wave source to generate the therapeutic ultrasonic wave.
A means for driving the ultrasonic probe to generate ultrasonic waves for imaging, an echo of a first ultrasonic wave from the therapeutic ultrasonic wave generation source through the ultrasonic probe, and a first ultrasonic wave from the ultrasonic probe. Receiving means for receiving the echo of the second ultrasonic wave, and first filter means for extracting the first component in the first specific band corresponding to the fundamental frequency of the therapeutic ultrasonic wave from the output of the receiving means. And a second within a second specific band according to the fundamental frequency of the ultrasonic wave for imaging.
Second filter means for extracting the above component from the output of the receiving means, means for individually amplifying the first component and the second component, and the amplified first component and the amplified component And a means for constructing an image based on the second component.

The first specific band includes a frequency corresponding to the maximum energy density in the spectrum of the echo of the therapeutic ultrasonic wave.

The ultrasonic therapy apparatus according to the present invention comprises a therapeutic ultrasonic wave generation source having resonance characteristics with respect to a first frequency,
An ultrasonic probe having a resonance characteristic for a second frequency, and a drive signal having a drive frequency between the first frequency and the second frequency for generating the therapeutic ultrasonic wave. Means for supplying to the ultrasonic source, means for driving the ultrasonic probe in order to generate the ultrasonic wave for imaging, echo of the therapeutic ultrasonic wave and the ultrasonic wave for imaging via the ultrasonic probe It comprises a receiving means for receiving the echo and a means for forming an image based on the output of the receiving means.

The drive frequency is determined based on the product of the frequency spectrum corresponding to the resonance characteristic of the therapeutic ultrasonic wave generation source and the frequency spectrum corresponding to the resonance characteristic of the ultrasonic probe.

The ultrasonic therapeutic apparatus according to the present invention comprises a therapeutic ultrasonic wave generating source, an ultrasonic probe, and first driving means for driving the therapeutic ultrasonic wave source to generate the therapeutic ultrasonic wave. Second driving means for driving the ultrasonic probe to generate an ultrasonic wave for imaging; and an echo of the first ultrasonic wave from the therapeutic ultrasonic wave generation source received via the ultrasonic probe. Means for forming an intensity distribution of the therapeutic ultrasonic wave and a tomographic image in the subject based on the echo of the second ultrasonic wave from the ultrasonic probe; and heat generation above a predetermined temperature based on the intensity distribution. And a means for estimating a treatment area to be treated.

The estimating means estimates the treatment area by correcting at least one of the position and the size of the focus area on the intensity distribution.

It further comprises means for displaying a marker representing the treatment region on the intensity distribution or the tomographic image.

At least one of the amplitude of the drive signal supplied from the first drive means to the therapeutic ultrasonic wave generation source, the duration of the drive signal, and the peak intensity in the intensity distribution is displayed. Means are further provided.

The ultrasonic therapy apparatus according to the present invention comprises a therapeutic ultrasonic wave source, an ultrasonic probe, and means for driving the therapeutic ultrasonic wave source to generate a therapeutic ultrasonic wave focused on a focal point. Means for driving the ultrasonic probe to generate an ultrasonic wave for imaging; and a first from the therapeutic ultrasonic wave generation source received via the ultrasonic probe.
Means for forming an intensity distribution of the therapeutic ultrasonic wave and a tomographic image in the subject based on the ultrasonic wave echo of the second ultrasonic wave and the second ultrasonic wave echo from the ultrasonic probe, and based on the intensity distribution Means for detecting the focal region of the therapeutic ultrasonic wave, means for forming the focal point of the therapeutic ultrasonic wave at a first focal position and a second focal position, and the means corresponding to the first focal position. And a means for displaying, on the tomographic image, a composite area of the first focus area and the second focus area corresponding to the second focus position.

The ultrasonic therapy apparatus according to the present invention comprises a therapeutic ultrasonic wave generation source, an ultrasonic probe, a means for driving the therapeutic ultrasonic wave source to generate the therapeutic ultrasonic wave, and an imaging ultrasonic wave. Means for driving the ultrasonic probe to generate an echo of a first ultrasonic wave from the therapeutic ultrasonic wave source received via the ultrasonic probe and a second echo from the ultrasonic probe. Means for constructing the intensity distribution of the therapeutic ultrasonic wave and the tomographic image in the subject based on the echo of the ultrasonic wave, and the space of the intensity distribution for the tomographic image based on the difference in the propagation path of the ultrasonic wave And a means for correcting a physical shift.

The ultrasonic therapy apparatus according to the present invention comprises a therapeutic ultrasonic wave generating source, an ultrasonic probe, a means for driving the therapeutic ultrasonic wave source to generate the therapeutic ultrasonic wave, and an imaging ultrasonic wave. Means for driving the ultrasonic probe to generate an echo of a first ultrasonic wave from the therapeutic ultrasonic wave source received via the ultrasonic probe and a second echo from the ultrasonic probe. Means for forming an intensity distribution of the therapeutic ultrasonic wave and a tomographic image in the subject based on the echo of the ultrasonic wave, and a spatial distribution of the intensity distribution with respect to the tomographic image due to the difference in the propagation path of the ultrasonic wave. In order to correct the deviation, the generation timing of the therapeutic ultrasonic wave with respect to the imaging ultrasonic wave is adjusted.

[0054]

BEST MODE FOR CARRYING OUT THE INVENTION The present invention will be described below based on preferred embodiments. The ultrasonic treatment apparatus includes a calculus breaking apparatus that focuses ultrasonic waves to break stones, and a thermotherapy apparatus that focuses ultrasonic waves to heat an affected part such as cancer and necrosis. Here, a thermotherapy device will be described as an example.

(First Embodiment) FIG. 1 is a block diagram of an ultrasonic therapeutic apparatus according to the first embodiment. The ultrasonic applicator 1 has a therapeutic ultrasonic wave generation source 2 for generating therapeutic ultrasonic waves. The therapeutic ultrasonic wave generation source 2 has, for example, a plurality of piezoelectric elements. In that case, the plurality of piezoelectric elements are arranged in an arc shape. The ultrasonic waves generated from the plurality of piezo elements are focused on the center of the arc. This focus point is called the geometric focus. A hole is made in the vicinity of the center of the arc of the therapeutic ultrasonic wave generation source 2, and an imaging probe 16 for generating an ultrasonic wave for imaging is inserted therein. A bag 5 containing the coupling liquid 4 is provided on the front side of the therapeutic ultrasonic wave generation source 2. The ultrasonic waves generated from the therapeutic ultrasonic wave generation source 2 and the imaging probe 16 pass through the coupling liquid 4 and propagate to the patient 3.

Here, one piezo element will be described as constituting one channel, but a plurality of neighboring piezo elements may constitute one channel.

The synchronizing circuit 18 supplies the first synchronizing signal to the pulse generating circuit 12. The pulse generation circuit 12 has a first
Signal pulses of the fundamental frequency f1 are periodically generated in accordance with the first synchronizing signal. The first fundamental frequency f1 matches the resonance frequency corresponding to the thickness of the piezoelectric element of the therapeutic ultrasonic wave generation source 2. The first fundamental frequency f1 is, for example, 1.
7 MHz. The signal pulse is supplied to the RF amplifier 14 via the changeover switch 13. When imaging the intensity distribution (in the operation mode B), the changeover switch 13 is connected to the B side.

The RF amplifier 14 amplifies the signal pulse,
Generate a drive pulse. The drive pulse is periodically applied to the piezo element of the therapeutic ultrasonic wave generation source 2 via the matching circuit 15. As a result, ultrasonic waves for intensity distribution are generated.

The ultrasonic wave for intensity distribution has a first fundamental frequency f.
It is periodically generated from the therapeutic ultrasonic wave generator 2 in a band centered on 1. The echo of the ultrasonic wave for intensity distribution is received by the imaging probe 16.

The continuous wave generating circuit 11 continuously generates a continuous signal of the first fundamental frequency f1. The continuous signal is supplied to the RF amplifier 14 via the changeover switch 13.
When actually treating (in the operation mode C), the changeover switch 13 is connected to the C side. The RF amplifier 14 amplifies the signal pulse and continuously generates a drive signal. The amplitude of this drive signal is larger than the amplitude of the drive pulse for the intensity distribution. The drive signal is continuously applied to the piezoelectric element of the therapeutic ultrasonic wave generation source 2 via the matching circuit 15. The therapeutic ultrasonic wave is continuously generated from the therapeutic ultrasonic wave generation source 2 in a band centered on the first fundamental frequency f1 and focused at a focal point to cause abnormal tissue such as cancer to generate heat and necrosis.

The imaging probe 16 has an array of a plurality of minute piezo elements. The imaging probe 16 may be of any type for sector scan, linear scan, and other scans. Here, the description will be made for sector scanning.

The piezo element of the imaging probe 16 has a first fundamental frequency f of ultrasonic waves for treatment and intensity distribution.
It has sensitivity peaks in both the low frequency band including 1 and the high frequency band including the second fundamental frequency f2 of the ultrasonic wave for imaging. For this reason, the piezo element of the imaging probe 16 has a two-layer structure or a hybrid structure as described in Japanese Patent Laid-Open No. 4-212599.
The two-layer structure piezo element is formed by stacking a piezo element element having a thickness corresponding to the first fundamental frequency f1 and a piezo element element having a thickness corresponding to the second fundamental frequency f2 with a common electrode interposed therebetween. Become. The piezo element of the hybrid structure is the first
A piezoelectric element having a thickness corresponding to the fundamental frequency f1 of
A piezo element element having a thickness corresponding to the second fundamental frequency f2 is arranged in parallel. Electrodes are formed on the front and back surfaces of each piezoelectric element.

The synchronizing circuit 18 supplies the second synchronizing signal to the transmitting circuit 17. The transmission circuit 17 includes a pulse generator, a transmission delay circuit, and a pulser. The pulse generator periodically generates a signal pulse of the second fundamental frequency f2 according to the second synchronizing signal. The second fundamental frequency f2 is different from the first fundamental frequency f1 and coincides with the resonance frequency according to the thickness of the piezo element of the imaging probe 16. Here, the case where the second fundamental frequency f2 is higher than the first fundamental frequency f1 will be described. Second fundamental frequency f2
Is, for example, 3.5 MHz. The signal pulse is distributed to the number of channels, the ultrasonic wave is focused into a beam by the transmission delay circuit, and the delay time required for oscillating the ultrasonic beam in a predetermined direction is given to each channel and sent to the pulsar. Be done. The pulser amplifies the signal pulse and generates a drive pulse. The drive pulse is periodically applied to the piezo element of the imaging probe 16. As a result, ultrasonic waves for imaging are generated. The echo of this ultrasonic wave is received by the imaging probe 16. The reception signal is supplied to the reception delay circuit 20 for each channel via the preamplifier 19. The reception delay circuit 20 determines the reception directivity by giving a delay time to the reception signals of the respective channels and adding them.

The reception signal from the reception delay circuit 20 is supplied to the B mode processing unit 22 via the echo filter 21. The B-mode processing unit 22, based on the received signal, B-mode image data (tissue tomographic image data),
Intensity distribution data representing a spatial distribution of the intensity of the therapeutic ultrasonic wave is generated. The B-mode image data and the intensity distribution data are displayed on the CRT 29 via the digital scan converter (DS-C) 28.

The received signal from the reception delay circuit 20 is passed through the echo filter 21 and the pulse Doppler unit 2
7 as well. The pulse Doppler unit 27 is
Quadrature detection circuit, analog-digital converter, M
It is composed of a TI filter, an autocorrelator, and a calculation unit, and generates color Doppler image data based on the received signal. The color Doppler image data is displayed on the CRT 29 via the digital scan converter 28.

As shown in FIG. 2, the echo filter 21
Has a high pass filter (HPF) 30 and a low pass filter (LPF) 31. The B-mode processing unit 22 includes a high frequency processing circuit 32H and a low frequency processing circuit 32H.
Has L and. The high frequency component of the received signal is supplied to the high frequency processing circuit 32H via the high pass filter 30.
The high frequency processing circuit 32H generates B mode image data based on the high frequency component. The low frequency processing circuit 32L generates intensity distribution data based on a low frequency component (a component corresponding to the first fundamental frequency f1). High frequency processing circuit 32
H and the low-frequency processing circuit 32L are respectively provided with Sensitive Ti for equalizing the change in attenuation depending on the depth.
It is composed of a me control (STC), a log amp, a detection circuit, and an analog-digital converter.

Next, the operation of this embodiment will be described. This operation has three operation modes A, B, and C. In the operation mode A, the therapeutic ultrasonic wave generation source 2 is not driven and the imaging probe 16 is driven. A cross section near the patient's body 7 to be treated is ultrasonically scanned through the imaging probe 16. According to this operation mode A, the body to be treated 7 is confirmed on the B mode image, and an initial treatment plan is prepared.

Next, the operation mode B is executed. The changeover switch 13 is connected to the B side. In the operation mode B, the therapeutic ultrasonic wave generation source 2 is driven and the imaging probe 16 is also driven. An ultrasonic wave for intensity distribution is generated from the therapeutic ultrasonic wave generation source 2 in accordance with the first synchronization signal. Imaging ultrasonic waves are generated from the imaging probe 16 a certain time after the rising of the second synchronization signal.

As shown in FIG. 3, the propagation path of the ultrasonic wave for intensity distribution and the propagation path of the ultrasonic wave for imaging are different. Therefore, it is necessary to adjust the irradiation timings of the respective ultrasonic waves so that the echoes of the intensity distribution ultrasonic waves reflected at the focus and the echoes of the imaging ultrasonic waves reflected at the focus reach the imaging probe 16 at the same time. is there. Therefore, as shown in FIG. 4, the second synchronization signal is
The frequency is the same as that of the first synchronization signal, but the phase is shifted. That is, the time difference ΔT between both sync signals
The difference between the irradiation timing of the ultrasonic waves for intensity distribution and the irradiation timing of the ultrasonic waves for imaging is the difference between the distance from the therapeutic ultrasonic wave generation source 2 to the focal point and the distance from the imaging probe 16 to the focal point. The system controller 9 adjusts the time so that the difference is divided by the speed of sound of ultrasonic waves. This time difference ΔT realizes that the ultrasonic waves for intensity distribution and the ultrasonic waves for imaging reach the focus at the same time.

The echo of the ultrasonic wave for intensity distribution and the echo of the ultrasonic wave for imaging are received by the imaging probe 16. The echo of the ultrasonic wave for intensity distribution contains many low frequency components corresponding to the first fundamental frequency f1. The echo of the ultrasonic wave for imaging contains many high frequency components corresponding to the second fundamental frequency f2.

As described above, the piezo element of the imaging probe 16 is sensitive to both the first fundamental frequency f1 of the ultrasonic waves for intensity distribution and the second fundamental frequency f2 of the ultrasonic waves for imaging. high. The piezo element of the conventional imaging probe 16 has high sensitivity to the second fundamental frequency f2 of the ultrasonic waves for imaging, but has low sensitivity to the first fundamental frequency f1 of the ultrasonic waves for intensity distribution.
Therefore, conventionally, the harmonic component contained in the echo of the ultrasonic wave for intensity distribution is mainly targeted for intensity distribution imaging, and the image quality is low. The harmonic components are emphasized by the non-linearity of the propagation of ultrasonic waves. The improvement of the image quality of the intensity distribution is realized by increasing the intensity of the intensity distribution ultrasonic wave. However, increasing the intensity of the ultrasonic wave for intensity distribution promotes the occurrence of cavitation in the focus, and there is a risk of causing considerable damage to the tissue in the focus region due to the shock wave generated at the time of its collapse, which is not preferable. . On the other hand, in the present embodiment, the piezo element of the imaging probe 16 has the first fundamental frequency f1 of the ultrasonic wave for intensity distribution and the second fundamental frequency f1 of the ultrasonic wave for imaging.
It is highly sensitive to both the fundamental frequency f2 and Therefore, it is possible to improve the image quality of both the intensity distribution and the B-mode image without causing damage to the tissue as much as possible and without degrading the time resolution. Further, the improvement of the image quality of the intensity distribution can be realized by increasing the reception sensitivity by adjusting the gain. In this case, in FIG. 2, at least one gain adjusting circuit is inserted in the path between the echo filter 21 and the B-mode processing unit 22, and preferably one gain adjusting circuit is inserted in each path.

The reception delay circuit 20 gives a delay time to each channel, and the reception signal generated by the addition is supplied to the echo filter 21. The received signal mainly has a low frequency component corresponding to the fundamental frequency f1 of the ultrasonic wave for intensity distribution and a high frequency component corresponding to the second fundamental frequency f2 of the ultrasonic wave for imaging. The high pass filter 30 of the echo filter 21 extracts a high frequency component from the received signal. The low pass filter 31 of the echo filter 21 extracts a low frequency component from the received signal. High frequency processing circuit 32
H produces a B-mode image based on the high frequency components.
The low frequency processing circuit 32L generates an intensity distribution based on the low frequency component. Further, the low frequency processing circuit 32L may extract a region of a pixel group that exceeds a predetermined threshold in the intensity distribution as a practical focus and display only this practical focus.

Since the low frequency component and the high frequency component are separately processed in this manner, the first gain is applied to the low frequency component and the second gain different from the first gain is applied to the high frequency component. Apply the gain and apply the appropriate S for each component.
TC can be realized. This is because the ultrasonic attenuation factor depends on the frequency.

Next, in the operation mode C, therapeutic ultrasonic waves having a higher intensity than the ultrasonic waves for intensity distribution are continuously generated from the therapeutic ultrasonic wave generating source 2 to treat the affected area.

In general, the ultrasonic waves generated from the therapeutic ultrasonic wave generation source 2 are focused closer to the focal point as the harmonic components are increased.
Therefore, in the case where the intensity distribution is imaged based on the higher harmonic component contained in the echo of the ultrasonic wave for intensity distribution as in the conventional case, there is a problem that the focal region is displayed narrower than it actually is. On the other hand, in the present embodiment, since the intensity distribution is imaged based on the subharmonic component (the component corresponding to the first fundamental frequency f1) that is often included in the echo of the ultrasonic wave for intensity distribution, the actual intensity distribution is Therefore, the reliability of the quantitative evaluation can be improved, and the estimation of the heat generation region and the like can be performed with high accuracy based on the intensity distribution.

(Second Embodiment) FIG. 5 is a block diagram of an ultrasonic therapeutic apparatus according to a second embodiment. FIG.
In FIG. 2, the same parts as those in FIG. The therapeutic ultrasonic wave generation source 33 employs a piezo element having sensitivity peaks at both the first fundamental frequency f1 corresponding to the therapeutic ultrasonic wave and the second fundamental frequency f2 corresponding to the imaging ultrasonic wave. ing. This piezo element is realized by the above-mentioned two-layer structure or hybrid structure.

The high frequency pulse generation circuit 34 periodically generates a signal pulse of the second fundamental frequency f2. This second
The signal pulse of the fundamental frequency f2 of
It is applied to the piezo element of the therapeutic ultrasonic wave generation source 33 through the amplifier 4, the switch 36 and the high frequency matching circuit 35 in this order. Thereby, the ultrasonic waves for intensity distribution are periodically generated. The continuous wave generating circuit 11 has a first fundamental frequency f1.
The continuous signal of is continuously generated. This continuous signal of the first fundamental frequency f1 is applied to the piezo element of the therapeutic ultrasonic wave generation source 33 through the switch 13, the RF amplifier 4, the switch 36, and the low frequency matching circuit 37 in this order. As a result, therapeutic ultrasonic waves are continuously generated.

The system controller 9 performs the same operation. In the operation mode B for imaging the intensity distribution, both the switch 13 and the switch 36 are connected to the B side. In the operation mode C in which treatment is actually performed, both the switch 13 and the switch 36 are connected to the C side.

In the operation mode B, the therapeutic ultrasonic wave generation source 33 is driven at the second fundamental frequency f2. An ultrasonic wave for intensity distribution is generated from the therapeutic ultrasonic wave generation source 33 in a high frequency band centered on the second fundamental frequency f2. The echo of the ultrasonic wave for intensity distribution has many high frequency components corresponding to the second fundamental frequency f2. The imaging probe 16 is highly sensitive to the second fundamental frequency f2.

Therefore, the same effect as that of the first embodiment can be obtained.

(Third Embodiment) FIG. 6 is a block diagram of an ultrasonic therapeutic apparatus according to the third embodiment. In FIG. 6, the same parts as those in FIG. 1 are designated by the same reference numerals and the description thereof will be omitted.

The ultrasonic diagnostic section 40 has an STC, a log amp, a detection circuit, and an analog-digital converter, like the B-mode processing unit 22 of FIG. The ultrasonic diagnostic unit 40 further includes a frequency information analysis unit 41 for acquiring frequency information.

Also in this embodiment, as in the first embodiment, the intensity distribution ultrasonic waves from the therapeutic ultrasonic wave generation source 2 and the imaging ultrasonic waves from the imaging probe 16 are focused. The timing of each occurrence is adjusted so that they arrive at the same time. In this embodiment, the accuracy of this simultaneity is improved.

The temperature sensor 42 is provided to measure the temperature of the coupling liquid 4. The calculation unit 44 calculates the sound velocity of the ultrasonic wave in the coupling liquid 4 based on the temperature of the coupling liquid 4 measured by the temperature sensor 42. The position sensor 43 realized by a rotary encoder or the like measures the difference between the distance from the surface of the piezo element of the therapeutic ultrasonic wave generation source 2 to the focal point and the distance from the surface of the piezo element of the imaging probe 16 to the focal point. It is provided to do so.

The system controller 9 corrects the phase difference (time difference ΔT) between the first synchronizing signal and the second synchronizing signal based on the calculated sound velocity and the measured difference in distance. This improves the accuracy with which the intensity distribution ultrasonic wave from the therapeutic ultrasonic wave generation source 2 and the imaging ultrasonic wave from the imaging probe 16 simultaneously reach the focal point.

FIG. 7 shows the configuration of the frequency information analysis unit 41 shown in FIG. The piezo element of the imaging probe 16 has a resonance characteristic that it is highly sensitive to the second fundamental frequency f2. This is equivalent to a high-pass filter that attenuates low-frequency components corresponding to the first fundamental frequency f1 contained in many echoes of the ultrasonic waves for intensity distribution. An equalizer 51 for compensating for this filter characteristic is provided in front of the frequency spectrum analysis unit 50.

FIG. 8 is an explanatory view of the function of the equalizer 51. The spectrum of the ultrasonic echo for intensity distribution is
Is higher in the fundamental wave band centered on the fundamental frequency f1 and in the higher harmonic band centered on the high frequency corresponding to an integral multiple (n · f1) of the first fundamental frequency f1. The sensitivity characteristic of the imaging probe 16 is the second fundamental frequency f.
High at 2. The spectrum of the received signal received by the imaging probe 16 is the frequency spectrum of the echo of the ultrasonic wave for intensity distribution, and the imaging probe 16
It is expressed as the product of the frequency characteristics of Equalizer 51
Approximately shapes the spectrum of the received signal with respect to the spectrum of the echo of the ultrasonic wave for intensity distribution.

The frequency spectrum analysis unit 52 subjects the received signal from the equalizer 51 to fast Fourier transform processing,
Generate a spectrum and determine the area of a specific band. By performing this for multiple points, the intensity distribution is generated. The specific band is a fundamental wave band, a harmonic wave band, or both bands. The imaging unit 53 assigns hue or luminance to the intensity distribution according to the size of each point.

The echo filter 54 receives the second signal from the received signal.
Is a band-pass filter that allows the higher harmonic components contained in the higher harmonic band centered on the fundamental frequency f2 of FIG. The image information processing unit 55 generates a B-mode image (B-mode image) based on the harmonic component that has passed through the echo filter 54.

The adder circuit 56 superimposes the spatial distribution of ultrasonic energy on the B-mode image. The frequency spectrum analysis unit 52 may calculate the spread degree (dispersion) of the spectrum for multiple points and obtain the spatial distribution of the dispersion of the spectrum. The higher the intensity of therapeutic ultrasonic waves, the more high-frequency components are generated.
Therefore, the spatial distribution of the variance is close to the intensity distribution. Further, the frequency spectrum analysis unit 52 may obtain the barycentric position of the spectrum for multiple points.

The system controller 9 estimates the temperature distribution based on the obtained intensity distribution. The tissue at the focal point of the therapeutic ultrasound heats up and becomes necrotic. The temperature depends on the ultrasonic absorption rate of tissue, thermal conductivity, intensity of therapeutic ultrasonic waves, irradiation time, and the like. The ultrasonic absorption rate and the thermal conductivity are input by the operator via the console 10. The ultrasonic absorption rate and the thermal conductivity are selectively read from the memory 45 in which the ultrasonic absorption rate and the thermal conductivity are stored for each part (organ). The ultrasonic absorption rate may be calculated based on the received signal. The intensities of the echo from the front of the focus and the echo from the focus are compared, and the ultrasonic attenuation rate is calculated based on this comparison result and the ultrasonic diffusion parameter according to the propagation distance. The ultrasonic absorption rate is calculated based on the above. The intensity of therapeutic ultrasound is obtained from the intensity distribution. The irradiation time is set by the operator.

The system controller 9 quantitatively estimates the temperature by applying the ultrasonic absorption rate, the thermal conductivity, the intensity of the therapeutic ultrasonic wave, and the irradiation time to the heat transport equation. This estimation is performed for multiple points near the focus. As a result, a spatial distribution of the estimated temperature (temperature distribution) is generated. The temperature distribution is displayed on the CRT 29 while being superimposed on the B-mode image. From the temperature distribution, extract the area above the heat-denatured necrosis temperature of the cancer cells (treatment area of about 50-60 ° or more), and enclose this area with a solid line or dotted line, color it, or shade it. May be. The operator can predict a region denatured by heat, a region to be damaged, and the like based on the temperature distribution.

The system controller 9 can make a plan for treating the range of the body to be treated designated by the operator on the B-mode image.
The system controller 9 recognizes the range of the body to be treated by dividing it into a predetermined number of areas (divided areas). 1 in one treatment
The focus intensity and the irradiation time are determined by the system controller 9 so that the treatment of one divided region is completed.
The extracted treatment area is enlarged / reduced in consideration of the ultrasonic absorption rate and the thermal conductivity while changing the focal intensity and the irradiation time. The focus intensity and irradiation time corresponding to the treatment area when they coincide with the divided area are selected.

Furthermore, in the present embodiment, the driving energy (first driving energy) required to obtain the focal intensity (first focal intensity) of the therapeutic ultrasonic waves required for the treatment, that is, the therapeutic energy The amplitude of the drive signal to be applied to the piezoelectric element of the ultrasonic wave generation source 2 can be obtained. this is,
In the present invention, this is because the focus intensity can be measured quantitatively. First, the drive energy (second drive energy) at the time of intensity distribution imaging and the focus intensity (second focus intensity) obtained thereby are stored in the memory 45. The focus intensity and the driving energy have a substantially proportional relationship. Therefore, the first drive energy is calculated by multiplying the second drive energy by the result of dividing the first focus intensity by the second focus intensity. This calculation is performed by the system controller 9. By generating the drive signal according to the obtained first drive energy, the first focus intensity can be obtained.

FIG. 9 shows the intensity distribution when there is a strong reflector of ultrasonic waves in the propagation path of therapeutic ultrasonic waves. When there is a strong reflector of ultrasonic waves in the propagation path, it is clinically important to detect this because the focus strength is reduced or the strong reflector is a heating element such as bone. In FIG. 9, the therapeutic ultrasonic wave propagates in the living body toward the focal point 60 along the propagation path 61. This propagation route 6
A strong reflector 63 is placed at a position deviated from the central axis 62 in FIG.
If so, the intensity distribution 64 is distorted and is not symmetrical as shown in FIG. The same applies when there is an ultrasonic absorber. One cause of the distortion of the intensity distribution 64 is that some therapeutic ultrasonic energy reaches the focal point by the strong reflector 63. If the strong reflector 63 exists not only on the two-dimensional imaging surface but also in the conical propagation path of the therapeutic ultrasonic wave, the intensity distribution 6
4 is distorted. Based on the shape of the intensity distribution 64, the operator can determine the presence or absence of a strong reflector or a strong absorber in the propagation path of the therapeutic ultrasonic wave. Furthermore, the system controller 9
However, the presence or absence thereof may be determined based on the result of comparison between the shape of the measured intensity distribution and the shape designated in advance, or the left-right symmetry of the shape of the measured intensity distribution. When the system controller 9 determines that it is present, the system controller 9 displays the system warning message 65 on the CRT 29 and issues a warning sound in order to present this presence to the operator. The system controller 9 also activates a safety function that forcibly prohibits the start of treatment.

The above-mentioned function for safety can also be performed by measuring the ultrasonic wave intensity in the focal region.
This method is effective even when there are strong reflectors or absorbers of ultrasonic waves in a plane that passes through the central axis of the two-dimensional imaging screen and is perpendicular to the screen. As mentioned above, the piezo element group 2
The energy of the focus area can be predicted from the driving energy of the.
At that time, if the ultrasonic attenuation factor in the living body is also taken into consideration, more accurate energy in the focus region can be predicted. In this way, the ultrasonic intensity in the focal area predicted in advance is compared with the ultrasonic intensity in the actually acquired focal area, and if the intensity difference is larger than the preset value, , It is possible that a part of the ultrasonic energy is scattered by the strong reflection pair (or strong absorber) of the ultrasonic waves and does not reach the focal point. . Alternatively, based on this information, configure a safety device to prevent starting treatment,
It may be incorporated into the system.

Further, the system controller 9 judges whether or not the propagation path of the therapeutic ultrasonic wave due to refraction or the like is distorted based on the intensity distribution, and when distorted, issues a warning. If the deviation is within the two-dimensional imaging plane, the deviation can be visually confirmed from the distortion of the intensity distribution. However, when the deviation direction is out of the two-dimensional imaging plane, the deviation cannot be visually confirmed. The system controller 9 compares the actual focus intensity with the expected intensity calculated from the driving energy and the like, and when the difference deviates from the predetermined range, the propagation path of the therapeutic ultrasonic wave is distorted. It is judged that the operator is present and this is presented to the operator.

If the difference between the actual focus intensity and the expected intensity is within a predetermined allowable range, the system controller 9 outputs a message that the treatment can be performed.

Next, a method of suppressing the influence of the intensity distribution imaging on the living body and improving the frame rate will be described. The acoustic energy of the ultrasonic waves for intensity distribution is lower than that of the therapeutic ultrasonic waves, and it is considered that the degree of influence on the living body is relatively low. However, if the number of rasters is reduced by narrowing the scan range of the intensity distribution imaging to at least include the vicinity of the geometric focus, the number of times the intensity distribution ultrasonic waves are applied to one frame is reduced. The influence of can be suppressed. Even when the scan for the B-mode image and the scan for the intensity distribution are alternately performed, the scan range of the intensity distribution imaging is narrowed and the number of rasters is reduced, so that The frame rate can be improved. On the other hand, even if the display area of the intensity distribution image is narrowed, since the propagation path of the therapeutic ultrasonic wave is narrower than the area of the normal in-vivo imaging, the intensity distribution imaging is not significantly affected. Such switching of the scanning range is performed by the control of the system controller 9 triggered by the operator inputting the switching instruction to the system controller 9 via the console 10. In addition, before the start of treatment, intensity distribution imaging is performed on the full-scale screen, and after confirming the safety in the propagation path of ultrasonic waves, the intensity distribution imaging area can be narrowed or limited to the focus area only. It is also possible to use the method of switching the display method during treatment.

(Fourth Embodiment) FIG. 10 is a block diagram showing the main parts of an ultrasonic therapeutic apparatus according to the fourth and third embodiments. 10, the same parts as those in FIG. 7 are designated by the same reference numerals and the description thereof will be omitted. A filter 70 for mainly removing a shift component due to blood flow from a received signal is provided in front of the frequency spectrum analysis unit 52 via a switch 71. The Doppler effect due to the blood flow shifts the frequencies of the ultrasonic waves for imaging and the ultrasonic waves for intensity distribution by several kHz. As schematically shown in FIG. 11, this shift band is a band centered on a frequency obtained by adding or subtracting several kHz to the first fundamental frequency f0, and several kHz to the second fundamental frequency f2.
It is defined as the band centered on the frequency that is adjusted.

The filter 70 sufficiently attenuates or removes the shift components within these shift bands. The filter 70 is composed of, for example, a plurality of high-pass filters and a plurality of low-pass filters. The filter 70 is not limited to this configuration as long as it realizes the function of sufficiently attenuating the shift component within the shift band. The filter 70 removes the shift component slightly apart from the fundamental frequency. Generally, the frequency difference between the imaging ultrasonic wave and the intensity distribution ultrasonic wave is 1 MHz or more, and a harmonic component is also included. Since the bandwidth is extremely wide, even if the shift component is removed, the signal strength does not extremely decrease, and thus high image quality is maintained. By adjusting the band to be removed by the filter 70, it is possible to remove the shift component other than the blood flow due to the moving body such as the heart wall.

By switching the switch 71, it is possible to select whether or not the shift component is removed. This switching is triggered by the operator inputting an instruction to the system controller 9 via the console 10.

(Fifth Embodiment) FIG. 12 is a block diagram of an ultrasonic therapeutic apparatus according to a fifth embodiment. FIG.
In FIG. 6, the same parts as those in FIG. As shown in FIG. 13, a therapeutic ultrasonic wave generator 8
In No. 0, the circular flat plate-shaped piezo element 81 is divided in the radial direction and the circumferential direction. In other words, the therapeutic ultrasonic wave generator 8
In No. 0, a plurality of piezoelectric elements 81 are arranged in a circular flat plate shape. Here, it is described that one piezo element 81 constitutes one channel, but a plurality of neighboring piezo elements 81 may constitute one channel.

One ultrasonic treatment section 46 is provided for each piezo element 81 so that the plurality of piezo elements 81 can be independently driven for each channel. The ultrasonic treatment section 46 is composed of a matching circuit, an RF amplifier, a continuous wave generation circuit, a pulse generation circuit, and a switching circuit between the continuous wave generation circuit and the pulse generation circuit. The synchronization circuit 18 individually supplies synchronization signals having different phases to the plurality of ultrasonic treatment units 46 so that the ultrasonic waves generated from the plurality of piezoelectric elements 81 are focused at the focal point. In addition, on the perpendicular line from the center point of the circular flat plate of the plurality of piezo elements 81,
A point having a predetermined depth is called a reference focus. The reference sync signal corresponds to this reference focus.

The synchronizing circuit 18 is the system controller 9
According to the control of 1, the phase of the synchronization signal supplied to each of the plurality of ultrasonic treatment units 46 can be changed. This change in phase realizes moving the focus from the position of the reference focus to another position. When the focus is moved from the reference focus position to another position, the acoustic pressure at the focus changes with respect to the acoustic pressure at the reference focus. The system controller 9 controls the RF amplifier of the ultrasonic treatment section 46 to adjust the amplitude of the drive signal in order to compensate for this acoustic pressure change.

Here, consider a case where the focal point of the therapeutic ultrasonic wave is deviated from the set position due to refraction or the like. Since the intensity distribution ultrasonic pulse and the imaging ultrasonic pulse have different propagation paths and angles of propagation with respect to the living body, they may have different refraction amounts. However, since the ultrasonic waves are the same, the difference in the degree of refraction is not so large, and is about several mm in the lateral direction at the depth of focus.

Therefore, the system controller 9 performs the following work. The focus position of the ultrasonic wave for intensity distribution is changed from the initial position. The focal position of the ultrasonic wave for intensity distribution is changed in a spiral shape within a range of a sphere having a radius of several mm centered on the position of the treatment target. At that time, the intensity distribution from the focus position on the image is measured as the reflected wave intensity of the ultrasonic pulse for imaging. The maximum reflected wave intensity is selected for each focus position. The maximum reflected wave intensity is compared with the estimated focus intensity to determine whether the difference is outside the allowable range. When the difference between the maximum reflected wave intensity and the estimated focus intensity is within the allowable range, the treatment start state is activated by the delay control corresponding to the maximum reflected wave intensity.
With this, the refraction amount of the ultrasonic pulse for intensity distribution imaging is corrected to the refraction amount of the ultrasonic pulse for imaging,
The difference between the two disappears. On the other hand, when the difference between the maximum reflected wave intensity and the estimated focus intensity deviates from the allowable range, a warning is output and the treatment start state is not activated.

The frequency information analysis unit 41 measures the treatment area based on the intensity distribution. The treatment area is defined as an area where heat generated by the therapeutic ultrasonic waves is high. The treatment area is slightly spatially offset from the focus. The echo of the ultrasonic wave for intensity distribution contains harmonic components in addition to the fundamental wave component. As shown in FIG. 14, the harmonic component is a signal component within the harmonic band. The harmonic band is a band centered on a frequency that is an integral multiple of the first fundamental wave frequency f1 of the intensity distribution ultrasonic wave and the therapeutic ultrasonic wave. The waveform of ultrasonic waves is distorted as the sound pressure level increases. This distortion produces harmonic components. That is, it can be presumed that a portion containing a large amount of harmonic components corresponds to a region where the sound pressure level is high, and this region has a high risk of heat generation. The frequency information analysis unit 41 extracts a harmonic component from the received signal. An intensity distribution is generated based on the extracted harmonic components. A region exceeding a predetermined intensity is extracted as a treatment region based on this intensity distribution. The state of the delay control is adjusted so that the position of the extracted treatment region matches the position of the body to be treated.

Here, as shown in FIG. 15, the treatment area 1
Consider the case where 03 is displaced with respect to the body 102 to be treated. Here, a three-dimensional ultrasonic image is generated. Regarding the generation of a three-dimensional ultrasonic image, see JP-A-61-20964.
Since this is a well-known technique disclosed in Japanese Patent Laid-Open No. 3 and Japanese Patent Application Laid-Open No. 5-300910, description thereof will be omitted. The CRT 29 includes a three-dimensional ultrasonic image 100, a three-dimensional coordinate axis 101, an object to be treated 102, and a three-dimensional coordinate 104 indicating a treatment area 103.
Is displayed. For example, this coordinate has a point 105 on the three-dimensional image as the origin (0,0,0). It is assumed that the coordinates of the treated object 102 are (0,8,0) and the coordinates of the treatment area 103 are (-1,6,0). Treatment area 103
The system controller 9 controls the synchronizing circuit 18 to change the state of delay control based on the spatial shift between the coordinates of 1 and the coordinates of the body to be treated 102, and executes the intensity distribution imaging in this state. This operation is repeated until the coordinates of the treatment area 103 match the coordinates of the treatment subject 102.
When both coordinates match, the treatment is started in the state of the delay control.

As shown in FIGS. 16 (a) and 16 (b), the extracted treatment region 103 has a rectangular marker 110a.
Alternatively, the focus may be displayed as the circular marker 110b so as to be distinguishable. The distinction is not limited to the difference in shape, and may be the difference in hue. Further, FIG. 16 (c)
As shown in, the marker 110c may be displayed in which the intensity change of the intensity distribution generated based on the harmonic component is represented by a hue change, a color intensity change, a brightness change, or a contour line.

(Sixth Embodiment) FIG. 17 is a block diagram of an ultrasonic therapeutic apparatus according to the sixth embodiment. FIG.
In FIG. 11, the same parts as those in FIGS. The plurality of piezoelectric elements forming the therapeutic ultrasonic wave generation source 2 can be individually driven by the corresponding drive circuits 120. The drive circuit 120 is connected to the system controller 9 and the drive power supply 121, and supplies a drive signal to the corresponding piezo element based on a control signal from the system controller 9.

Here, a stone treatment will be described. First, in order to match the focal point of the therapeutic ultrasonic wave with the calculus, an object to be treated (calculus) on the B-mode image reconstructed by the ultrasonic image diagnostic unit 40 based on the reception signal acquired by the imaging probe 16. Is confirmed. The position of the body to be treated is input by the operation of the console 10 by the operator. The coordinates of the body to be treated are the system controller 9
Is calculated by Based on the calculated coordinates of the body to be treated, the system controller 9 sets the delay control state, that is, the time difference of the drive timing between the piezo elements, that is, the piezo element, so that the focus of the therapeutic ultrasonic wave matches the body to be treated. Calculate the delay time for each element. The input of the position of the body to be treated may be automatic detection as disclosed in, for example, Japanese Patent Application No. 4-261420.

Conventionally, the calculation of the delay time of each piezo element has been performed on the assumption that the ultrasonic wave propagation process has linearity. The therapeutic ultrasonic wave (shock wave), which is extremely strong enough to crush stones, has a strong nonlinear effect in the process of propagation of the ultrasonic wave. Therefore, in the conventional calculation method, the focal point actually formed is displaced from the calculated focal point position. This deviation is not large on the reference line vertically lowered from the center point of the therapeutic ultrasonic wave generation source 2, but becomes large when the focus is off the reference line. The reason why such a deviation occurs is that the distance from each piezo element to the focal point deviated from the reference line differs between the piezo elements.

FIG. 18 shows the change of the shift amount with respect to the change of the distance from the reference line to the calculated focal point. In addition,
The displacement on the side closer to the therapeutic ultrasonic wave generation source 2 is represented as positive, and the displacement on the far side is represented as negative. There is no change in the deviation amount (□) of the normal ultrasonic waves for imaging. On the other hand, the amount of displacement (x) of the therapeutic ultrasonic wave, which is much stronger than the imaging ultrasonic wave, increases as the focus moves away from the reference position. The reason for this is that the difference in the propagation distance to the set position described above increases as the distance from the reference line increases, and the influence of the non-linear effect that occurs in the ultrasonic wave propagation process increases.

In the present embodiment, the coordinates of the body to be treated are corrected based on the amount of deviation, and the delay time of each piezo element is calculated as in the conventional manner so that the focus is formed on the corrected coordinates. As a result, the focus can be matched with the object to be treated with high accuracy. In the memory 45, the distance from the reference line,
The shift amount is stored for each of many combinations of ultrasonic wave intensities (amplitudes of drive signals). The system controller 9 obtains the distance between the designated position of the body to be treated and the reference line, reads the deviation amount corresponding to this and the ultrasonic intensity (amplitude of the drive signal) from the memory 45, and based on this deviation amount. The position of the body to be treated is corrected, and the delay time of each piezo element is calculated so that the focus is formed at the corrected position. Further, in the memory 45, a correction value of the delay time corresponding to the amount of deviation is stored for each of many combinations of the distance from the reference line and the ultrasonic wave intensity (amplitude of the drive signal). The delay time calculated for each piezo element may be corrected in the conventional manner so that the focus is formed at the position of the treatment target.

Since the focus is not formed in a pinpoint, but in a range having a certain width, the settable focus positions may be discrete based on the focus size.

Instead of storing the deviation amount or the correction value in the memory 45, the system controller 9 may calculate the deviation amount or the correction value based on the distance from the reference line and the ultrasonic intensity. Good.

(Seventh Embodiment) FIG. 19 is a block diagram of a tracking type ultrasonic therapy apparatus according to the seventh embodiment. 19, the same parts as those in FIG. 17 are designated by the same reference numerals and the description thereof will be omitted. For example, as disclosed in Japanese Patent Publication No. 6-26549, there is a technique for tracking the focus of therapeutic ultrasonic waves using a phased array technique for an object to be treated that moves due to respiratory motion such as kidney stones. It is well known. The treatment target position detection unit 140 detects the position of the treatment target in almost real time. This detection technique is also disclosed in Japanese Patent Application No. 4-261420, etc.
It is well known. For example, a method of calculating a difference between two consecutive frames of a B-mode image obtained by ultrasonic waves or CT and detecting the position of the body to be treated based on the result, a method of detecting the peak position of the ultrasonic echo as a stone, etc. There is.

The position information of the body to be treated is supplied from the treatment position detecting means 140 to the system controller 9 constantly or periodically. The delay time of each piezo element is calculated so that the focus is formed at the position of the body to be treated. At this time, by applying the correction described in the sixth embodiment, it is possible to achieve high accuracy. The focus can be tracked to the treated body.

Note that instead of moving the focal position of the therapeutic ultrasonic wave by delay control as described above, a method of locally adjusting the refractive index of the acoustic lens and moving the focal position may be adopted. .

(Eighth Embodiment) The eighth embodiment relates to eliminating noise mixed in a B-mode image when the B-mode image is constructed during treatment. Noise reduction is achieved by the ultrasonic diagnostic unit 40 in the above-described embodiment.

As shown in FIG. 20 (a), the therapeutic ultrasonic waves are periodically generated as burst waves in the first cycle.
The imaging ultrasonic pulse is periodically generated in a second cycle that is significantly shorter than the first cycle, and the echo is received before the transmission of the next imaging ultrasonic pulse. Transmission and reception of imaging ultrasonic waves are repeated for each of the N rasters. Hereinafter, a scan is defined as a transmission / reception operation for one frame in which transmission / reception of imaging ultrasonic waves is repeated N times while sequentially changing rasters. The echo of the therapeutic ultrasonic pulse is significantly stronger than the echo of the imaging ultrasonic wave. The reception gain is set based on the echo of the ultrasonic wave for imaging. Therefore, as shown in FIG. 20B, when the scanning and the irradiation of the therapeutic ultrasonic burst are simultaneously performed,
B corresponding to the period during which the therapeutic ultrasonic pulse is generated
A part 153 on the mode image 150 is displayed as an extremely high brightness area. This embodiment provides several methods for removing this noise. Any one of a plurality of methods may be adopted, or all of the plurality of methods may be enabled and selectable by the operator.

(First Method) FIG. 21 is a time chart showing the relationship between the irradiation timing of therapeutic ultrasonic waves and the scanning timing. The therapeutic ultrasonic pulse is periodically generated as a burst wave in the first cycle. The cross-section of the patient is periodically scanned with imaging ultrasound waves at a unique period (frame period) independent of the first period.

22A to 22D schematically show B-mode images of three frames generated by continuous scanning. The noise fringes 161 due to at least one therapeutic ultrasonic wave are mixed in one frame of B-mode image. A synchronization signal for determining the irradiation timing of the therapeutic ultrasonic pulse is supplied from the system controller 9 to the ultrasonic diagnostic unit 40. The ultrasonic diagnostic unit 40
The range in which the noise stripe 161 is generated on the B-mode image is obtained based on the frame period and the synchronization signal. The ultrasonic diagnostic unit 40 removes the range of the noise fringes 161 from the latest one frame of the B-mode image 160c, and the range of the plurality of B-mode images 160a and 160b generated immediately before the relevant B-mode image 160c. By supplementing from
One-frame B-mode image 160 without noise stripes 161
Create d.

(Second Method) FIG. 23 is an explanatory diagram of the second method. Reference numeral 171 indicates the irradiation timing of the therapeutic ultrasonic burst. The ultrasonic diagnostic apparatus 40 suspends the scanning with the ultrasonic waves for imaging while the therapeutic ultrasonic burst is being emitted. Ultrasonic diagnostic equipment 40
Restarts scanning from the raster following the raster at the time of interruption when the irradiation of the therapeutic ultrasonic burst is stopped.

(Third Method) FIG. 24 is an explanatory diagram of the third method. Reference numeral 181 indicates the irradiation timing of the therapeutic ultrasonic burst. The ultrasonic diagnostic apparatus 40 does not receive an echo, does not write the received signal to the image memory, or does not display it on the CRT while it is being irradiated with the therapeutic ultrasonic burst. Thereby, B
In the mode image, the noise part appears black, but the white noise part disappears.

(Fourth Method) FIGS. 25A to 25
FIG. 26F and FIG. 26A to FIG. 26D are explanatory views of the fourth method. 25 (b), 25 (d) and 25 showing time charts showing the temporal relationship between the irradiation timing of the therapeutic ultrasonic burst and the scanning timing.
25 (f), FIG. 26 (b) and FIG. 26 (d) are respectively shown in FIG.
(A), FIG. 25 (c), FIG. 25 (e), FIG. 26 (a),
It corresponds to FIG. 25 (a) and 25 (b)
As shown in FIG.
The scan timing is set with respect to the irradiation timing of the therapeutic ultrasonic burst so that noise stripes 191 are generated at both ends of 0a. As shown in FIGS. 25 (c) and 25 (d), the ultrasonic diagnostic apparatus 40 scans with respect to the irradiation timing of the therapeutic ultrasonic burst so that a noise stripe 191 is generated in the central portion of the B-mode image 190b. Plan the timing. As shown in FIGS. 25 (e) and 25 (f), the ultrasonic diagnostic apparatus 40 uses the therapeutic ultrasonic burst so that the noise fringes 191 are generated in portions other than both end portions and the central portion of the B-mode image 190c. The scan timing is set with respect to the irradiation timing. As shown in FIGS. 26 (a) and 26 (b), the ultrasonic diagnostic apparatus 40 has a target portion (for example, a focus).
201 is not hidden by noise stripe 202, and B mode image 2
The scan timing is set with respect to the irradiation timing of the therapeutic ultrasonic burst so that the noise stripe 202 is generated in the right half of 00. As shown in FIGS. 26C and 26D, the ultrasonic diagnostic apparatus 40 includes a target portion (for example, a focus) 20.
1 is not hidden by the noise stripe 202, and the B-mode image 200
The scan timing is set with respect to the irradiation timing of the therapeutic ultrasonic burst so that the noise stripe 202 is generated in the left half of the.

(Ninth Embodiment) FIG. 27 shows the configuration of an ultrasonic therapeutic apparatus according to the ninth embodiment. In the ninth embodiment, the ultrasonic therapeutic apparatus is used together with the magnetic resonance diagnostic apparatus. In ultrasonic hyperthermia treatment, it is important to confirm the positional consistency between the affected area and the heat-generating area with high accuracy before the treatment is started.

The magnetic resonance diagnostic apparatus can measure the temperature distribution by utilizing the temperature dependence of the chemical shift and the relaxation time T1 ((Y. Ishihara et al,: Proc. 11th An.
n.SMRM Meeting, 4803, 1992), (H.Kato et al.:'Po
ssible application of noninvasive thermometry for
hyperthemia using NMR ', International Conference on
Cancer Therapy by Hyperthemia, Radiation and Drug
s, Kyoto, Japan (Sept.1981))).

Further, the magnetic resonance diagnostic apparatus can measure a local region or a region having an arbitrary shape by the selective excitation technique ((CJ Hardy, and HECline, Journal of Magnetic
Resonance, vol.82, pp.647-654,1989), (J.Pauly et
al.:'Three-Dimensional πPulse ', Proc. 10th Ann.SM
RM Meeting, 493, 1991)).

By the way, since the living body has movements such as respiratory movements and body movements, it is important to monitor erroneous irradiation of normal tissue and current temperature of the affected area in real time during hyperthermia treatment with ultrasonic waves. Attempts have been made to measure a two-dimensional temperature distribution with a diagnostic device and utilize it for the above monitoring. In hyperthermia, the affected part is instantaneously heated to a high temperature, and therefore this monitoring requires a fairly high time followability (real-time property). Also,
In addition to temperature, it is necessary to obtain data showing the therapeutic effect with high time resolution, and a measurement method that gives priority to time resolution is necessary.

However, in order to measure the temperature distribution of one frame, the magnetic resonance diagnostic apparatus requires, for example, the time required for one excitation (repetition time) times the number of encoding times in the spin echo method. Repeat time T
If R is 2 seconds and the number of encoding times is 128, it takes about 5 minutes. Even in the field echo method or the echo planar method, which is faster than the spin echo method, it takes several seconds to measure the temperature distribution of one frame. Furthermore, a time lag of about several seconds required for the image reconstruction processing is required before the temperature distribution is output from the imaging. Therefore, real-time monitoring by temperature distribution
It was difficult.

In order to increase the time resolution, it is possible to measure a one-dimensional temperature distribution instead of two-dimensional one. However, this method is not preferable because there is a problem in that the heat generation region deviates from the measurement line for measuring the one-dimensional temperature distribution. There is also a problem that the thickness of the slice thickness causes a partial volume effect, and the peak temperature is measured low. Furthermore, there is also a problem that it is not possible to check that overheat occurs in a portion other than the measurement line in the one-dimensional temperature distribution.

The purpose of the ninth embodiment is to enable temperature monitoring with high time resolution. FIG.
In, the static magnetic field magnet 211 is driven by the excitation power source 212 and applies a uniform static magnetic field in the z direction to the patient 213. The gradient magnetic field coil 214 is arranged in the static magnetic field magnet 211, is driven by the drive circuit 216, and linearly changes the magnetic field strength in three directions of x, y, and z orthogonal to the patient 213 on the bed 217. Gradient magnetic field Gx, G
Apply y and Gz. The radio frequency coil 218 is arranged in the gradient magnetic field coil 214. The high frequency coil 218 is supplied with a high frequency signal from the transmitter 219 via the duplexer 220 and generates a high frequency magnetic field. Receiver 221
Receives a magnetic resonance signal from the patient 213 via the high frequency coil 218 and the duplexer 220. As the high frequency coil 218, a saddle type coil, a distributed constant type coil, a quadrature coil or a surface coil is adopted. The duplexer 220 includes a transmitter 219 for the high frequency coil 218.
The radio frequency signal from the transmission unit 219 is transmitted to the radio frequency coil 218 during transmission, and the reception signal from the radio frequency coil 218 is guided to the reception unit 221 during reception.

The sequence controller 215 controls the drive circuit 216, the transmitter 219, and the receiver 221 to execute a predetermined pulse sequence. Receiver 221
Detects the received signal and limits the band. The received signal is sent to the data collection unit 222. Data collection unit 22
2 converts the received signal into a digital signal and supplies it to the electronic computer 223. The electronic computer 223 has a receiving unit 221.
The MR image and the temperature distribution are reconstructed by applying the two-dimensional Fourier transform processing to the data from the above. The MR image and temperature distribution are supplied to and displayed on the image display 225.

The ultrasonic applicator 226 has a plurality of piezoelectric elements 227 for generating therapeutic ultrasonic waves.
The therapeutic ultrasonic waves are applied to the patient 213 via a coupling liquid such as deaerated water contained in the water bag 228.

A power source 229 for driving the ultrasonic applicator 226 is controlled by the electronic computer 223.
Ultrasonic applicator 226 so that the focus can be moved
Are supported by a moving mechanism 230 composed of a multi-joint mechanical arm or the like. The focus movement may be realized by phase control for the plurality of piezo elements 227.

An imaging probe 231 is attached to the center of the ultrasonic applicator 226. The imaging probe 231 is driven by the ultrasonic diagnostic unit 232, scans the cross section of the patient, and reconstructs and displays B-mode image data and intensity distribution data based on the obtained reception signal. The timing of this scan is controlled by the electronic computer 223. The B-mode image data and the intensity distribution data are transferred from the ultrasonic diagnostic section 232 to the electronic computer 22.
Sent to 3. The electronic computer 223 synthesizes the B-mode image or intensity distribution with the MR image or temperature distribution.

The electronic computer 223 finds the maximum intensity point on the basis of the intensity distribution, accumulates the intensity distribution continuously obtained to obtain the input energy of the ultrasonic wave, and obtains a one-dimensional temperature distribution by the magnetic resonance diagnostic apparatus. A two-dimensional or three-dimensional temperature distribution is obtained based on the cumulative distribution.

FIG. 28 shows the flow of slice plane determination processing. 29, 30, and 32 show supplementary views thereof. An intensity distribution (first intensity distribution) for the first cross section including the focus is generated (S1, S2). The coordinates of the maximum intensity point (first maximum intensity point) in the first cross section are obtained based on the first intensity distribution (S3). An intensity distribution (second intensity distribution) regarding a second cross section including the first maximum intensity point and orthogonal to the first cross section is generated (S4, S5). The coordinates of the maximum strength point (second maximum strength point) in the second cross section are obtained based on the second strength distribution (S6). The coordinates of the true maximum intensity point are detected based on the coordinates of the second maximum intensity point and the position of the second cross section (S7). A plane centered on the true maximum intensity point is determined as a slice plane of the magnetic resonance diagnostic apparatus (S8). Alternatively, a line centered on the true maximum intensity point is determined as an imaging line of the magnetic resonance diagnostic apparatus. The determined slice plane or line is imaged by the magnetic resonance diagnostic apparatus, and a two-dimensional or one-dimensional temperature distribution is reconstructed. The echo planar method is adopted as the imaging method. The temperature distribution is obtained by subtracting the phase image obtained before the treatment and the phase image obtained after the treatment and converting the phase change into the temperature based on the temperature dependence of the chemical shift. As for the temperature distribution, the intensity change of the image signal accompanying the temperature change of the relaxation time T1 is acquired in advance,
This is obtained by converting the change in the image signal into temperature.

By determining the slice planes or lines as described above, a two-dimensional or one-dimensional temperature distribution centered on the maximum intensity point can be obtained. In order to eliminate the influence of the partial volume effect from the converted temperature, it is preferable to make a correction with the expected distribution shape acquired in advance. As shown in FIG. 31, the peak temperature in the temperature distribution is displayed on the MR image (tissue image). In addition, spatial temperature changes are displayed as hue changes or contour lines. If the intensity distribution is one-dimensional, as shown in FIG.
It may be displayed as a graph by superimposing it on the R image.

The maximum intensity point of ultrasonic waves almost coincides with the maximum exothermic point. Therefore, it is possible to reliably monitor the state of the maximum heat generation point. If the temperature or the shape of the temperature distribution is different from the expected one, a malfunction such as insufficient coupling between the imaging probe 231 and the patient 213 is expected. In this case, the electronic computer 223 forces the treatment. Cancel, sound an alarm, and display a warning message.

FIG. 34 shows an example of a pulse sequence for obtaining a one-dimensional temperature distribution. Slice selection is applied in the x direction, followed by slice selection in the y direction.
As a result, a magnetic resonance signal from a columnar local portion along the z direction is detected. The position information in the z direction is made by frequency encoding. Thereby, the one-dimensional temperature distribution in the z direction is acquired. Of course, the oblique imaging method may be used to acquire the one-dimensional temperature distribution in any direction.

Although the ultrasonic scan planes for searching for the maximum intensity point are two orthogonal planes, the positional relationship between the two planes is not limited to orthogonal. For example, two parallel ultrasonic scan planes may be used. The maximum intensity points of the two parallel ultrasonic scan planes are compared, the intensity distribution of the other plane is acquired in the vicinity of the larger point, and the same comparison is repeated until the maximum intensity point becomes smaller. There is also a method in which the intensity distribution between the two is acquired when it becomes smaller and the flow of similar comparison is repeated to sequentially search for the position of the maximum intensity point.

FIG. 35 shows the flow of processing for obtaining a two-dimensional temperature distribution based on the one-dimensional temperature distribution and the therapeutic ultrasonic irradiation time by the magnetic resonance diagnostic apparatus. First, multiple intensity distributions for multiple scan planes are acquired (S
11). The three-dimensional coordinates of the maximum intensity point are detected based on the plurality of intensity distributions (S12). Next, the one-dimensional temperature distribution regarding the line including the maximum intensity point detected in S12 is measured by the magnetic resonance diagnostic apparatus (S15). The maximum heating temperature in the one-dimensional temperature distribution is detected (S1
6). Based on the measured intensity distribution and the irradiation time of the therapeutic ultrasonic wave, the ultrasonic energy input so far is obtained. Further, by obtaining the temperatures at other points based on the shape of the intensity distribution, the two-dimensional temperature distribution can be estimated (S17). The proportional relationship between the input ultrasonic energy and temperature is relatively reliable. In addition, MR
The reliability can be further improved by measuring the maximum heating temperature by the one-line temperature measurement by I every arbitrary time and feeding back the maximum temperature point during irradiation to the temperature distribution. Even if the patient moves during treatment, the intensity distribution shape, therapeutic ultrasonic irradiation time, and MRI are as described above.
By using the 1-line temperature measurement with, it is possible to grasp the temperature distribution situation in two dimensions and in real time.
More accurate treatment becomes possible.

Note that the two-dimensional temperature distribution obtained in real time may be used to control the irradiation conditions of therapeutic ultrasonic waves. For example, as shown in FIG. 36, a change in the temperature distribution expected from the irradiation conditions is compared with the actually measured temperature distribution, and when a difference between the two exceeds a certain threshold value, or an unexpected portion is detected. When it is overheated, stop irradiation, turn off the alarm, or display the alarm. Alternatively, the ultrasonic wave irradiation intensity is controlled so as to eliminate this. For example, when the measured temperature is lower than the set temperature, the irradiation intensity is controlled to be increased.

As described above, according to the ninth embodiment,
In the ultrasonic treatment apparatus using MRI, the temperature of the treatment target can be accurately measured during treatment irradiation, and the temperature distribution can be acquired at high speed.

(Tenth Embodiment) FIG. 37 shows a tenth embodiment.
1 shows a configuration of an ultrasonic irradiation device according to the embodiment. FIG.
7, the same parts as those in FIGS. 1 and 6 are designated by the same reference numerals and the description thereof will be omitted. The ultrasonic diagnostic unit 40 has an MTI (Mov
ing Target Indicatoin) operation unit 400 is provided. The MTI calculation unit 400 detects the movement information of the moving body such as the blood flow based on the phase difference of the received signal due to the movement of the measured object.
In order to obtain the dimensional distribution, it is composed of a quadrature detection circuit, an A / D converter, an MTI filter, an autocorrelator, and a calculation unit. The two-dimensional distribution of movement information is displayed in color on the display unit inside the ultrasonic diagnostic unit 40. Since the MTI calculator 400 is generally well-used, the details of its operation are omitted here. For example, Medical Ultrasonic Equipment Handbook edited by Japan Electronic Machinery Manufacturers Association, Corona Company, P172-
See P175, etc.

The synchronizing signal 101 (first synchronizing signal 101) is transmitted from the ultrasonic diagnostic section 40 to the timing signal generating circuit 180.
Is supplied. The synchronization signal 101 is defined as a pulse train in which a pulse having a predetermined pulse width is repeatedly generated at a constant cycle. The ultrasonic diagnostic unit 40 is irradiated with imaging ultrasonic waves from the imaging probe 16 after a certain time from the rise of the synchronization signal 101.

The timing signal generating circuit 180 generates the second synchronizing signal 102 based on the first synchronizing signal 101. The second synchronization signal 102 is defined as a pulse train in which a pulse having a predetermined pulse width is repeatedly generated in the same cycle as the first synchronization signal 101. Here, the second
At the same time as the rising edge of the synchronization signal 102, the intensity distribution ultrasonic wave is emitted. Therefore, the second synchronization signal 102 is
It is not synchronized with the first synchronization signal 101. Second synchronization signal 1
The time difference between 02 and the first synchronization signal 101 is set to dt. The time difference dt is adjusted by the system controller 9 so that the imaging ultrasonic wave and the intensity distribution ultrasonic wave reach the focus at the same time. The reference for calculating the time difference dt is as described in the first and second embodiments.

The second synchronizing signal 102 is supplied from the timing signal generating circuit 180 to the phase shifter 470 via the changeover switch 480. The phase shift unit 470 shifts the phase of the second synchronization signal 102 to generate the third synchronization signal 103.

FIG. 38 shows the structure of the phase shift unit 470. FIG. 39 shows a temporal relationship between the first synchronization signal 101 and the third synchronization signal 103. The phase shift unit 470 includes the control circuit 20.
3 is a control center, and includes programmable N-ary counter circuits 201 and 202, an input buffer circuit 204, a counter circuit 205, a reference clock generation circuit 206, a reference clock characteristic adjusting circuit 207, and an output buffer circuit 208. The third synchronization signal 103 is defined as a pulse train in which pulses having a predetermined pulse width are repeatedly generated. The reference clock generation circuit 206 generates a clock at a cycle of T2. T2 is a cycle sufficiently faster than the synchronizing signal 102, and can be arbitrarily set by the operator. T2
Is set to 1/100 of the sync signal 102, for example. The programmable N-ary counter circuit 201 generates a pulse each time the count number of the clock from the reference clock generation circuit 206 reaches N. This pulse is output as the third synchronization signal 103 via the output buffer circuit 208. It should be noted that N set in the programmable N-ary counter circuit 201 is sequentially increased each time the synchronizing signal 102 is input, and N is reset to 1 by a reset signal from the control circuit 203.

The reset signal output by the control circuit 203 is repeatedly generated at a cycle set by the operator. The operator sets so that a reset signal is output each time the synchronizing signal 102 is input N2 times, and this N2 is set in the programmable N-ary counter circuit 202. When the synchronizing signal 102 is input N 2 times, the programmable N-ary counter circuit 202 outputs a reset signal to the control circuit 203. This N2 setting can be changed at any time.

The waveform generator 460 uses the third synchronization signal 10
3, the drive pulse is repeatedly supplied to the therapeutic ultrasonic wave generation source 2 to repeatedly generate the intensity distribution ultrasonic pulse.

The transmission of the ultrasonic waves for imaging is performed after a fixed time has elapsed from the rising of the first synchronizing signal 101.

The second synchronizing signal 102 is generated by the timing signal generating circuit 180 in the same fixed cycle as the first synchronizing signal 101. The second synchronization signal 102 is generated by the timing signal generation circuit 180.
The difference from 1 is dt.

The third synchronizing signal 103 is generated by the phase shifter 470 based on the second synchronizing signal 102. Third
The synchronization signal 103 of the
A delay time in the range of T2 or more and less than N2 · T2 can be given. This delay time is incremented by T2 for each pulse of the second synchronization signal 102, and the first synchronization signal 101
When the maximum time corresponding to the period of is reached, it then returns to T2. The change in delay time is repeated in such a cycle.

The ultrasonic pulse for intensity distribution is repeatedly generated according to the third synchronizing signal 103. When the delay time is 0, the echo from the focus of the intensity distribution ultrasonic pulse is received by the imaging probe 16 at the same time as the echo from the focus of the imaging ultrasonic wave. When the delay time is not 0, the echo from the focal point of the therapeutic ultrasonic pulse is earlier than the echo from the focal point of the imaging ultrasonic wave by the delay time, and the imaging probe 1
6 is received. The delay time is increased by T2 each time a therapeutic ultrasound pulse is generated.

As a result, the phase of the received signal corresponding to the echo of the intensity distribution ultrasonic pulse changes every time the intensity distribution ultrasonic pulse is generated.

Since the echo component of the ultrasonic pulse for intensity distribution has a phase difference, it passes through the MTI filter and is imaged as an intensity distribution on the two-dimensional distribution of the movement information by the MTI calculator 400. In this way, the MTI calculation unit 400 can image the intensity distribution together with the blood flow image, for example.

Depending on the connection switching of the changeover switch 480, the second synchronizing signal 102 may be transferred to the phase shifter 470.
It is also possible to obtain the intensity distribution by passing it to the waveform generating section 460 and performing the normal B-mode processing. The phase shift unit 470 is not limited to the configuration of FIG. Further, in the above description, the delay time is explained to change regularly in the unit time T2, but the amount of change in the delay time may be random. This is because a jitter circuit is provided instead of the phase shift circuit 470. It is realized by making the pulse period of the second synchronization signal 102 irregular. Further, in the above, the phase difference is obtained by adjusting the generation timing of the ultrasonic pulse for intensity distribution, but this phase difference may be given to the received signal. Further, although the third synchronization signal is adjusted with the first synchronization signal as a reference, the third synchronization signal is fixed to a fixed cycle, and the cycle of the first synchronization signal is varied with the third synchronization signal as a reference. You may do it.

(Eleventh Embodiment) FIG. 40 shows the eleventh embodiment.
1 shows a configuration of an ultrasonic irradiation device according to the embodiment. FIG.
0, the same parts as those in FIG. 1, FIG. 6, and FIG.

The ultrasonic diagnostic section 40 includes a transmitting / receiving circuit 402,
Digital scan converter 412, CRT 413,
It has a B-mode processing system and an intensity distribution processing system. The B-mode processing system and the intensity distribution processing system share the transmission / reception circuit 402, the digital scan converter 412, and the CRT 413.

The B-mode processing system generates the B-mode image based on the received signal from the transmission / reception circuit 402.
It is composed of a detection circuit 409, a gain adjustment unit 410, and an analog-digital converter 411. Detection circuit 409
Detects the reception signal from the transmission / reception circuit 402. The gain adjustment unit 410 amplifies the detection signal from the detection circuit 409. The analog-digital converter 411 converts the amplified detection signal into a digital signal.

The intensity distribution processing system is composed of a quadrature phase detection circuit 414, a gain adjusting section 407, and an analog-digital converter 408 in order to generate an intensity distribution based on the received signal from the transmitting / receiving circuit 402.

The quadrature detection circuit 414 is composed of a mixing circuit 405 and a low-pass filter 406 in order to extract the component within the highest energy band (high energy band component) of the intensity distribution ultrasonic wave from the received signal. It The high energy band component is a component (fundamental wave component) within a band (fundamental wave band) centered on the fundamental frequency f1 or a component (harmonic band) centered on a high frequency that is an integral multiple of the fundamental frequency f1. (Harmonic component). The mixing circuit 405 multiplies the reception signal from the transmission / reception circuit 402 by the reference signal of the reference frequency supplied from the signal generation unit 502. The reference frequency is the fundamental frequency f of the therapeutic ultrasonic wave.
1 or an integral multiple (n · f1) thereof.

The quadrature detection circuit 414 can be replaced with a bandpass filter.

The received signal received by the imaging probe 16 is spectrally analyzed by the calculation section 44, the frequency component with the highest energy density is extracted from this spectrum, and the frequency or its nearby frequency is used as the reference frequency. You may ask. In this case, the system controller 9 controls the signal generation unit 502 so that the reference signal is generated from the signal generation unit 502 at the obtained reference frequency. By doing so, it becomes possible to detect the frequency of the highest energy density in the received signal. The detection of the frequency of the highest energy density may be repeated every time a received signal is received during the treatment, may be repeated at a fixed cycle, may be performed once before the treatment, and may be fixedly used thereafter. Alternatively, it may be adjusted by the operator.

The gain adjusting section 407 amplifies the detection signal from the quadrature detection circuit 414. The analog-digital converter 408 converts the amplified detection signal into a digital signal.

The B-mode image generated by the B-mode processing system and the intensity distribution generated by the intensity distribution processing system are combined into one frame by the digital scan converter (DSC) 412 and displayed on the CRT 413.

The B-mode image data and the intensity distribution data thus obtained are used in the digital scan converter 41.
2 is combined into one frame and displayed on the CRT 413.

In this way, the intensity distribution is generated from the high energy band components extracted from the received signal, and the high intensity region such as the focus is emphasized. Therefore, it is possible to check the positional relationship between the focus and the body to be treated and the irradiation of unnecessary high-intensity ultrasonic waves to the healthy part with high accuracy, and a safe and reliable treatment is realized.

Further, since the received signal and the high energy band component extracted from the received signal are processed separately, each gain can be adjusted individually.

(Twelfth Embodiment) FIG. 42 shows the configuration of an ultrasonic therapeutic apparatus according to the twelfth embodiment. FIG.
In FIG. 6, the same parts as those in FIGS. Ultrasonic diagnostic unit 40
Has a configuration of a general ultrasonic diagnostic apparatus including an analog unit, an FFT unit, an MTI calculation unit, and a display unit. The analog section has a quadrature phase detection circuit including a mixer 405 and a low-pass filter 406.

Under the control of the system controller 9, the changeover switch 601 is controlled by the oscillator and the signal generating means 50.
Either one of the two is connected to the mixer 405. The oscillator produces a first reference signal. Signal generating means 502
Generates a second reference signal. The frequency of the first reference signal is set within the frequency band of ultrasonic waves for imaging. The frequency of the second reference signal is set within the frequency band of the ultrasonic pulse for intensity distribution.

As in the tenth embodiment, a jitter for giving a jitter to the synchronization signal 102 that determines the generation timing of the ultrasonic pulse for intensity distribution so that the intensity distribution can be generated based on the output of the MTI filter. Addition unit 608
However, the timing signal generator 180 and the waveform generator 460
It is provided between and. Instead of providing the jitter adding unit 608, the MTI calculating unit may be separated during the intensity distribution imaging. In that case, since the number of transmissions per raster (one line forming an ultrasonic tomographic image) can be set to 1, the frame rate is improved, the real-time property is increased, and the temperature rise in the living body due to ultrasonic waves is suppressed. It has the effect of

In the two-dimensional color Doppler imaging, the first reference signal output from the oscillator is supplied to the mixer 405 via the changeover switch 601, and in the intensity distribution imaging, the second reference signal output from the signal generating means 502. The signal is supplied to the mixer 405 via the changeover switch 601.

At the time of two-dimensional color Doppler imaging, imaging is performed based on the high energy density frequency component in the echo of the ultrasonic waves for imaging,
At the time of intensity distribution imaging, imaging is performed based on the high energy density frequency component in the echo of the intensity distribution ultrasonic wave.

Therefore, two-dimensional color Doppler imaging and intensity distribution imaging can be performed with high accuracy.

FIG. 43 shows a processing procedure leading to intensity distribution imaging. First, the name of the imaging probe 16 attached to the ultrasonic diagnostic unit 40 is input from the operator to the system controller 9 via the console 10 (S21). The memory 45 stores frequency characteristics corresponding to the names of various types of imaging probes 16. The frequency characteristic corresponding to the name of the attached imaging probe 16 is stored in the memory 45.
Read from the system controller 9 (S2
2). The processing of S21 and S22 can be substituted for the processing (S23) in which the frequency characteristic of the imaging probe 16 attached to the ultrasonic diagnostic unit 40 is directly input from the operator to the system controller 9 via the console 10. Is.

The frequency characteristic of the therapeutic ultrasonic wave generating source 2, specifically, the resonance frequency peculiar to the therapeutic ultrasonic wave generating source 2 is input from the operator to the system controller 9 via the console 10 (S24). Ultrasonic source 2 for treatment
Drive frequency is calculated by the system controller 9 based on the frequency characteristic of the imaging probe 16 and the resonance frequency of the therapeutic ultrasonic wave generation source 2 (S2).
5). As shown in FIG. 44, the drive frequency fdrive is a resonance frequency of the therapeutic ultrasonic wave generator 2, a frequency within its band or an integral multiple of the resonant frequency of the therapeutic ultrasonic wave generator 2, and The frequency of the harmonic is within the high sensitivity band of the imaging probe 16.

The characteristics of the ultrasonic diagnostic section 40 are adjusted according to the drive frequency fdrive (S26). In particular,
The filter characteristics in the ultrasonic diagnostic unit 40 are adjusted by the system controller 9 according to the drive frequency fdrive. Next, intensity distribution imaging is started (S
27).

During the intensity distribution imaging, the therapeutic ultrasonic wave generating source 2 is driven by the driving signal of the driving frequency fdrive, whereby the transmitting efficiency by the therapeutic ultrasonic wave generating source 2 and the receiving efficiency by the imaging probe 16 are improved. The corresponding overall efficiency is improved. FIG. 45 shows a procedure for setting the reference frequency. An ultrasonic pulse for intensity distribution imaging is emitted from the therapeutic ultrasonic wave generation source 2 (S31), and the echo is received by the imaging probe 16 (S31).
32). The received signal is processed by the calculation unit 440 such as fast Fourier transform. As a result, a frequency spectrum is obtained (S33). In this frequency spectrum,
The frequency with the highest energy density is selected by the calculation unit 440 (S34). The oscillation frequency of the signal generator 502 is locked to a frequency slightly deviated from this frequency (S
35). The reference signal at the locked frequency is supplied from the signal generator 502 to the mixer 405 (S36).

Although the therapeutic ultrasonic wave generation source and the imaging probe are separately provided, the therapeutic ultrasonic wave and the intensity distribution ultrasonic pulse may be generated from the imaging probe. In this case, in order to generate the ultrasonic pulse for intensity distribution and the ultrasonic wave for imaging in a superimposed manner, the driving power of the piezo element is a superposition of the electrical signal for intensity distribution and the electrical signal for imaging.

(Thirteenth Embodiment) FIG. 46 shows the thirteenth embodiment.
1 shows a configuration of an ultrasonic therapy device according to the embodiment. FIG.
6, the same parts as those in FIGS. 1, 6 and 37 are designated by the same reference numerals, and the description thereof will be omitted. The ultrasonic diagnostic unit 40 reconstructs a B-mode image in the patient based on an RF circuit 51 for transmitting and receiving ultrasonic waves via the imaging probe 16 and a reception signal received by the imaging probe 16. Reconstructing unit 52, an ultrasonic condition imaging unit 53 that reconstructs the intensity distribution of the therapeutic ultrasonic wave based on the received signal received by the imaging probe 16, and a display that displays the B-mode image and the intensity distribution. And a portion 54.

The RF circuit 51 supplies a drive signal to the imaging probe 16 at a predetermined timing,
The reception signal received by the imaging probe 16 is amplified. Further, the RF circuit 51 extracts a signal component for intensity distribution from the received signal and outputs it to the ultrasonic distribution status imaging unit 53. This extraction is realized by a low pass filter, a band pass filter, or a quadrature detection circuit.

The display section 54 includes a treatment effect estimation section 61,
The distribution correction unit 62 is connected. Due to the effects of cavitation, changes in the acoustic characteristics of the tissue due to thermal denaturation, etc., the treatment area where thermal denaturation and necrosis actually occur shifts to the applicator 1 side with respect to the focal point 8. Further, the size of the treatment area depends on the input period of acoustic energy and does not match the size of the focus 8.

The treatment effect estimation section 61 determines the size and position of the treatment area. The treatment effect estimation unit 61 performs, on the display unit 54, processing necessary to display the treatment area marker in the determined size and at the determined position.

The distribution correction unit 62 carries out, on the display unit 54, the processing required to correct the spatial deviation of the intensity distribution for the B-mode image. The correction amount for correcting the spatial deviation of the intensity distribution differs depending on the position on the scan plane. This correction amount is calculated in advance as follows,
It is stored in the internal memory of the distribution correction unit 62. By considering the therapeutic ultrasonic wave generation source 2 as a collection of minute sound sources and superposing the ultrasonic waves emitted from the respective sound sources, the state of waves in the homogeneous medium can be obtained for each position. The correction amount is calculated based on the state of this wave. In FIG. 46, the position information of the intensity distribution is received from the display unit 54, but the position information of the intensity distribution may be received from the system controller 9.

Next, the operation of this embodiment will be described. First, the cross section including the body to be treated 7 is scanned with ultrasonic waves through the imaging probe 16, and the body to be treated 7 is drawn on the B-mode image. At this time, CT and M
It is possible to measure the shape of the body to be treated 7 using RI or the like, formulate a treatment plan, and perform treatment based on the contents.
In that case, a CRT which reproduces the treatment plan is separately prepared, the treatment plan is presented there, and the operator operates the device based on the instruction, or the treatment plan contents are stored in the memory 45 or the like in advance, The system controller 9 may sequentially call the contents to execute the treatment. In addition, by connecting the treatment planning device and the actual treatment room online, it is possible to perform treatment according to the treatment plan, and it is also possible to quickly respond to correction of the treatment plan in response to an unexpected situation during treatment. It is also possible to do so.

The position and angle of the imaging probe 16 are changed and the scan plane is moved. A plurality of B-mode images or a three-dimensional image constructed from the plurality of B-mode images confirms the three-dimensional shape of the treated body 7 and the existence of important organs, bones, etc. in the ultrasonic wave propagation path. . All B-mode image data is stored in the memory 45.

Next, based on at least one of the amplitude of the echo component of the therapeutic ultrasonic wave from the object to be treated 7 included in the received signal and the energy of the predetermined band, the irradiation condition of the therapeutic ultrasonic wave is determined by the system controller 9. Adjusted by. The irradiation conditions include the irradiation intensity, that is, the amplitude (peak voltage) of the drive signal input to the therapeutic ultrasonic wave generation source 2, and the irradiation time, that is, the duration of the drive signal. The echo component from the treated body 7 is extracted from the received signal by the calculation unit 440. This echo component is extracted by applying a time gate to the received signal at a timing according to the depth of the body to be treated 7. For this purpose only, the ultrasonic diagnostic unit 40 may be in the M mode or the B mode.

Based on the intensity of the echo component from the body to be treated 7, the ultrasonic absorption rate of the body to be treated 7, the attenuation rate of the ultrasonic waves to the body to be treated 7, the existence of important organs and bones in the propagation path, etc. hand,
The irradiation intensity and irradiation time are determined by the system controller 9.

The intensity of the echo component from the body to be treated 7, the ultrasonic absorption rate of the body to be treated 7, the thermal conductivity, the attenuation rate of the ultrasonic waves to the body to be treated 7, the important organs and bones in the propagation path, etc. The size of the treatment region is calculated by the treatment effect estimation unit 61 based on a plurality of parameters such as existence, irradiation intensity, and irradiation time.
In this calculation, data representing the size of the treatment area corresponding to each of the various combinations of the above plurality of parameters,
Alternatively, the size of the corresponding treatment area stored in the memory 45 may be read out via the system controller 9.

The intensity of the echo component from the body to be treated 7
Based on multiple parameters of ultrasonic absorption rate, thermal conductivity, attenuation rate of ultrasonic waves to the treated body 7, existence of important organs and bones in the propagation path, irradiation intensity, irradiation time The treatment effect estimation unit 61 calculates the amount of shift in which the treatment region shifts to the applicator 1 side with respect to the focus region. In this calculation, the data representing the deviation amount corresponding to each of various combinations of the plurality of parameters is stored in the memory 45, and the corresponding deviation amount data is read out to the treatment effect estimation unit 61 via the system controller 9. May be substituted for.

The treatment effect estimation unit 61 performs the processing necessary for displaying the marker of the treatment area in the determined size at the determined position on the display unit 54. FIG. 47 shows an example of the display screen of the CRT in the display unit 54.

Obviously, rather than displaying the focal point 8 of the therapeutic ultrasonic wave as it is, it is possible to estimate the therapeutic region based on the intensity distribution and display the therapeutic region to help achieve reliable treatment. As an example, the opening diameter is 110 [mm] and the inner diameter is 42 [m.
m], radius of curvature 100 [mm], resonance frequency 1.65M
Using a therapeutic ultrasonic source consisting of one Hz piezo element,
The electric energy input to the ultrasonic source is 400 [W],
It has been clarified by an experiment that, when it is set to 10 [s], a treatment area of about 2 [mm] with respect to the focus 8 shifts to the ultrasonic source side. So for such parameters,
A marker indicating the treatment region is displayed with a shift of 2 [mm] toward the applicator 1 side with respect to the focal point 8 obtained by the intensity distribution imaging.

The marker may be painted in a specific color, or may be displayed in a light color or a shade so that the original B-mode image does not disappear. Or,
Display only the outline of the treatment area that will be obtained,
Contour lines may be displayed according to the intensity distribution. A simpler geometrical shape, such as a cross or a rectangle, may be used so that the size of the graphic corresponds to the size of the treatment-scheduled region. At this time, the actual therapeutic ultrasonic focus may be displayed at the same time, or the planned ultrasonic irradiation intensity and the planned irradiation time may be displayed. Furthermore, of the reflection intensities obtained by intensity distribution imaging, the peak intensity from the focus 8 is displayed in real time (numerical value display, color bar display, A
If the mode is displayed, the operator adjusts the coupling state, the applicator tilt angle, and the approach direction, and the peak intensity becomes the highest (the state where the energy input to the focus 8 is the highest = the most efficient). It is possible to easily find out various ultrasonic irradiation conditions).

Next, while gradually shifting the focal point 8 of the therapeutic ultrasonic wave, it is confirmed whether or not the object to be treated 7 larger than the focal point 8 can be completely treated. The movement of the focal point 8 is realized mechanically, electronically, or a combination of both. Also, the operator can set the pitch of the shift on the console 1
It is specified via 0 or calculated by the calculation unit 440 based on the determined irradiation condition. Further, the order of shift may be sequentially moving to the adjacent region, or may be moved diagonally in order to suppress the influence of cavitation, or first from the farthest from the therapeutic ultrasonic wave source 2 to the front. You may shift in order.

In any of the above cases, finally, by setting the adjacent focus points so that the treatment areas corresponding to the focal points 8 of the individual therapeutic ultrasonic waves partially overlap each other, it is possible to ensure that all tumor cells are contained. It becomes possible to necrosis.
However, this is not the case when the intense ultrasound treatment is performed in combination with other treatment methods. For example, a method of cauterizing the periphery of a tumor by this method and treating the central part by another method has been considered.

It is also possible to calculate the amount of temperature increase in the treatment target area based on the total input energy, the diffusion of heat, the cooling effect of the blood flow, etc., and set the focus points with a certain interval. Is.

In any case, if the intensity distribution imaging is executed in the body to be treated 7 in accordance with the procedure of treatment and the expected individual treatment regions are collectively displayed before the actual treatment, the final treatment is performed. You can easily check the treatment area. FIG.
Shows the result shaded. This makes it easy to determine whether or not an untreated region has occurred. In addition, the coupling state between the applicator 1 and the living body, the presence or absence of obstacles of the strong reflector and the strong absorber in the propagation path of the therapeutic ultrasonic waves, and sufficient ultrasonic energy is applied to the focal point 8. Whether or not it can be predicted by the intensity distribution imaging at each focal position, so that the safety and certainty of the treatment is improved. The display of such a treatment area is shown in FIG.
As shown in FIG. 5, the process is performed for each of a plurality of images having different cross sections. This allows the operator to stereoscopically understand the expected treatment area. These images may be sequentially switched and displayed, or a three-dimensional image may be constructed and displayed.

As a result of the above, when it is recognized that the treatment status is inappropriate, the fact is displayed or the operator is notified by a warning sound, or the apparatus is locked so as not to shift to the treatment mode. You can also

Before the treatment, the inside of the body to be treated 7 is focus-scanned and the intensity distribution imaging is performed for each scan. The obtained irradiation parameters and other data are recorded and read out during the actual treatment. Although the treatment is executed, for example, as a simple method, the irradiation parameter may be determined by representing the data by the intensity distribution imaging when the center of the focal point 8 is aligned with the center of the treated body 7. Further, during the actual treatment, that is, immediately before the irradiation of the therapeutic ultrasonic wave at each focal position, the intensity distribution imaging may be performed, and the irradiation condition of the therapeutic ultrasonic wave may be determined from the data.

Next, the correction of the spatial distortion of the intensity distribution drawn by the intensity distribution imaging by the distribution correction unit 62 will be described. Intensity of the B-mode image and the therapeutic ultrasonic wave is obtained by irradiating the ultrasonic pulse from both the therapeutic ultrasonic wave generation source 2 and the imaging probe 16 and receiving the echo from the inside of the subject by the imaging probe 16. Distributions are acquired at the same time. Both ultrasonic pulses are generated at the timing when both pulses reach the center of the focus 8 at the same time.

As schematically shown in FIG. 48, the propagation distance (A) of the imaging ultrasonic wave returning from the imaging probe 16 to the imaging probe 16 via the reflection point P and the therapeutic ultrasonic wave generation source 2 The difference from the propagation distance (B) of the therapeutic ultrasonic wave from the reflection point P to the imaging probe 16 via the reflection point P increases as the reflection point P moves away from the focal point 8. In ultrasonic diagnosis, the depth is recognized by associating the time axis of the received signal with the axis in the depth direction, so that the intensity distribution is distorted. For example, the position of the point P in FIG. 48 is recognized as the point P ′ in front of the true position on the intensity distribution. This deviation amount is calculated by the system controller 9 or the calculation unit 440 based on the speed of sound and the propagation path.

The position of the intensity distribution is shifted by the correction amount corresponding to this shift amount and is combined with the B-mode image. Since the amount of deviation is a function of spatial position, the amount of distortion can be calculated immediately by substituting the position and the sound velocity for this function. In addition, like a normal ultrasonic diagnostic apparatus, the speed of sound in the living body is constant (for example, 1530 [m / m).
s]), the correction amount corresponding to the spatial position is stored in the memory 4
If the data is recorded in 5 and the like, and the contents of the memory are sequentially read and corrected for each position, a speedup of the correction can be expected.
Further, in addition to the method of performing correction when combining two types of images, a method of dividing a signal by a time gate and acquiring position data in advance by estimating a deviation amount when acquiring position data in the depth direction There is. In any case, the echo that reconstructs the B-mode image in the subject and the echo that reconstructs the intensity distribution imaging image are obtained within the same time gate, except when the echo from the focal center is acquired. Even echoes represent different depths of data.

(Fourteenth Embodiment) FIG.
1 shows a configuration of an ultrasonic therapy device according to the embodiment. FIG.
9, the same parts as those in FIGS. 1, 6, 37 and 46 are designated by the same reference numerals, and the description thereof will be omitted. In the present embodiment, the distortion of the intensity distribution is corrected by adjusting the generation timing of the ultrasonic pulse for intensity distribution. The distribution correction unit 62 is connected to the timing signal generation circuit 180.

[0209] The applicator 1 comprises a therapeutic ultrasonic wave generating source 2 and an imaging probe 16 which are arranged on a concave surface having a central hole. With such a shape, the focal region is formed as a three-dimensional shape obtained by rotating "X" around the center line. In this case, even if the spatial distortion at the place where the ultrasonic intensity is low is sacrificed, if the position is corrected by paying attention to the place where the ultrasonic intensity is high, a distribution shape having no practical problem can be obtained. That is, the distortion is corrected by paying attention to each point on the "X" shape. To achieve this,
As shown in FIGS. 50 (a) and 50 (b), the correction amount is converted from the distance dimension to the time dimension, and the irradiation timing of the ultrasonic pulse for intensity distribution emitted from the therapeutic ultrasonic wave generation source 2 is changed. Change by ΔT. More specifically, the highest intensity point on the “X” shape is focused on for each raster of the scan, and the amount of positional deviation at that position is divided by the speed of sound. The irradiation timing of the intensity distribution ultrasonic pulse is deviated from the timing with respect to the focus position by the division result ΔT. that time,
When there are a plurality of points on "X" for one raster, the point closest to the focus is used as a reference.

In this way, after the simulation (focus shift and intensity distribution imaging) immediately before the treatment is executed using this method, the hyperthermia treatment is actually started. At the time of treatment, a high energy ultrasonic burst that surely leads to heat-denatured necrosis of the tissue in 1 second or less is irradiated as therapeutic ultrasonic waves. At that time, a safe and reliable treatment is realized by executing the treatment in accordance with the above-mentioned treatment simulation.

That is, the parameters such as the focus shift pitch, the irradiation intensity, the irradiation time, etc. are set as in the above-mentioned treatment simulation. The sequence of ultrasonic irradiation in the treatment mode is focus shift, intensity distribution imaging, therapeutic ultrasonic irradiation, intensity distribution imaging, and the following sequence is repeated. In addition to this, intensity distribution imaging is performed only after irradiation of therapeutic ultrasonic waves, intensity distribution imaging is performed for each number of times of irradiation of therapeutic ultrasonic waves that is set arbitrarily, and irradiation of intensity distribution imaging and therapeutic ultrasonic waves is performed. There are various types of combination patterns, and the operator can set them according to the situation. Here, a case where intensity distribution imaging is performed before and after irradiation of therapeutic ultrasonic waves will be described.

First, the treatment area is adjusted to the target position by the focus shift. Next, intensity distribution imaging is performed with reference to the irradiation conditions determined by simulation.
After confirming again that sufficient energy is applied to the focal point and that there is no strong reflector of ultrasonic waves or important organs in the propagation path of the therapeutic ultrasonic waves, the process proceeds to irradiation of therapeutic ultrasonic waves. In this case, if a therapeutic ultrasonic wave is applied by the cavitation-suppressing irradiation method as described in Japanese Patent Application No. 6-248480, a reliable therapeutic result (heat degeneration region) can be obtained. By performing intensity distribution imaging again after the therapeutic ultrasonic irradiation, it can be confirmed whether or not the heat-denatured region is surely obtained.

That is, since the acoustic characteristics of the heat-denatured area are largely changed with respect to the surrounding undenatured cell area,
A large echo is obtained at the interface between the heat-denatured region and the native cell region, and the treated region can be detected by receiving and analyzing this echo. As a method for this, the echoes at the same position are compared before and after the treatment, and the portion having a large difference is the treated region. More roughly, the A mode of ultrasound may be used to confirm whether or not the treatment has been reliably performed. Further, the treated area may be detected by comparing the luminance information before and after the treatment from the B-mode image.

As described above, the safety in the ultrasonic wave propagation path and the state of energy input to the focal point 8 can be reconfirmed point by point just before the irradiation, and the treatment can be reliably achieved after the irradiation of the therapeutic ultrasonic wave. Since it can be confirmed using intensity distribution imaging whether or not it has been performed, safety and certainty of treatment can be improved. Further, this work can be executed in a short time because only the echo data obtained by the intensity distribution imaging performed for each focal position is analyzed. Next, the focus 8 is moved to the next treatment area based on the preset focus scan order, and the same treatment as described above is repeated to perform the next treatment. If the treated area is stored and displayed in a different color at the time of display so that it can be immediately visually discriminated, it becomes possible to see at a glance whether or not the treatment of all the treated body 7 is completed.

[0215] The movement of the patient may be a serious problem during treatment. If the patient moves during the treatment, the body to be treated 7, the treated area, and the focus 8
There is a possibility that the treatment will not proceed according to the treatment plan because the positional relationship with In that case, either the treatment plan is changed and the treatment is restarted from the beginning, or the treatment plan is changed but the treatment plan is newly reestablished and the treatment is restarted, or the treatment is returned to the original state. It is.
The first method is the simplest, but has the disadvantage of increasing the treatment time. The second or third approach requires identification of the treated area. As a method thereof, as described above, it is conceivable to detect reflected ultrasonic waves from the boundary surface of the treated region, and intensity distribution imaging can be used for realizing this. At that time, if the body surface or the like is used as the reference point, the treated site can be easily specified even if the patient moves.

Specifically, in the intensity distribution imaging immediately after the irradiation of therapeutic ultrasonic waves, the body surface of the patient 6 or the water bag 4 is
The timing at which the echo from the patient is obtained and the timing at which the echo from the treated area is obtained are measured. Since the propagation medium 5 is in front of the body surface or the water bag 4, it is extremely easy to detect the body surface or the water bag 4. Further, immediately after the treatment, the echo from the boundary surface of the treated region has an extremely large change amount as compared with that immediately before the treatment, and a large echo can be obtained, so that the discrimination is easy. From these, even if the patient 6 moves, it becomes easy to detect the treated area again due to the time relationship between the body surface or the water bag 4 and the boundary surface of the treated area. It should be noted that the B-mode luminance information and data before that (including RF data) may also be used for specifying the treated region. Further, whether or not the patient has moved may be added with a motion detector, and as a device therefor, an optical surveillance camera, a method for measuring a change in resistance of an elastic resistor wound around the patient, an optical fiber The photoplethysmography method and the like can be used.

Next, the display method will be described with reference to FIG. FIG. 51 shows an example of the display screen. As described in Japanese Patent Application No. 6-246843, in the treatment with strong therapeutic ultrasonic waves, a therapeutic ultrasonic wave source 2
On the other hand, it is desirable to perform cauterization from as far away as possible, that is, from the surface corresponding to the bottom surface of the treatment volume. The reason is that the acoustic characteristics of the tissue change due to heat denaturation, ultrasonic waves are reflected at the boundary surface and energy is absorbed by the heat denaturation region, and the ultrasonic wave is present in the region behind the heat denaturation region. This is because it is difficult for energy to reach them. In the case of such an irradiation method, there is a problem that it is difficult to capture a treatment image because the plane for performing treatment intersects the two-dimensional B-mode tomographic image.

In order to solve this problem, a B-mode image corresponding to the actual treatment execution surface is reconstructed from a plurality of B-mode images having different cross sections and displayed. The positional relationship between the imaging probe 16 and the display image is displayed.
It is reconstructed based on the B-mode image acquired while shifting the focus 8 in the simulation before the treatment.

FIG. 52 shows a plurality of scan planes. B-mode image data is acquired for each scan plane. These data are a collection of two-dimensional images,
One image has one-dimensional image information regarding a certain depth. If this one-dimensional image information is extracted from a plurality of image data and reconstructed, a B-mode image corresponding to the depth of interest can be reconstructed (C mode). When the treatment is performed based on the C-mode image, the focus 8 and the marker indicating the treatment planned area are displayed on the image. In this case, the focus mark is displayed as a circle, a circle, a cross, or the like.

Although the sector type imaging probe 16 is used here, a convex type probe may be used. Further, the closer to the probe 16, the narrower the imaged region becomes. Therefore, in order to obtain an ultrasonic image of an equal region that does not depend on depth, linear type (mechanical scanning type, electronic scanning type) imaging is performed. It is preferable to use a probe for use. Alternatively, a three-dimensional ultrasound image is reconstructed, a pseudo translucent image is reconstructed, and the surface or volume corresponding to the surface or volume treated by one irradiation is lightly colored or surrounded by a line. By doing so, the face of interest may be emphasized.

Next, as an example, a case where the treatment area is designated with reference to the B-mode image will be described. A plurality of B-mode images are acquired so as to include all of the planned region of the treated body 7. At that time, the operator uses the console 10,
Alternatively, a treatment planned area is designated on each B-mode image using a light pen, a mouse, a joystick, a trackball, and the like (not shown). By irradiating a therapeutic ultrasonic wave based on the designated treatment scheduled region, reliable treatment can be achieved even in the details of the boundary surface of the irradiation region. Here, a three-dimensional image may be constructed from the plurality of B-mode images. In addition, here, the method of designating the treatment region with reference to the ultrasonic image is described.
Line CT or MRI may be used.

Next, a method of accurately drawing a focus with respect to an actual focus position will be described. As described above, at the time of intensity distribution imaging, at the moment when the wavefront indicating the peak intensity of the ultrasonic pulse for intensity distribution emitted from the therapeutic ultrasonic source passes through the imaging probe 16, the imaging probe 16 performs imaging. The ultrasound pulse for imaging is synchronized with the ultrasound pulse for intensity distribution so that the ultrasound pulse is emitted.
The accuracy of this synchronization determines the accuracy of the focus position rendered by intensity distribution imaging. Here, an ultrasonic probe for picking up the ultrasonic pulse for intensity distribution is added to the extension surface of the surface on which the piezo elements are aligned on the imaging probe 16, or equivalently on the same surface. Either it is corrected by calculation so that it can be regarded as, or the imaging probe 16 is used as a pickup probe. In this way, by actually acquiring the ultrasonic pulse for intensity distribution imaging and performing feedback control, if the irradiation timing of the ultrasonic pulse for intensity distribution imaging from the therapeutic ultrasonic source is determined, it is possible to obtain extremely high accuracy. It is possible to depict various focal positions.

Next, a method for quantifying the echo intensity received by ultrasonic intensity distribution imaging will be described. The ultrasonic wave is attenuated as it propagates deeper into the patient 6, but similarly, as the echo from the deeper part of the living body is attenuated. Therefore, it is preferable to display the intensity distribution by weighting the echo intensity received by the imaging probe 16 according to the depth from the body surface. For example, when reconstructing an ultrasonic B-mode image, it is common practice to increase the amplification factor according to the depth.

Further, the patient information can be displayed on the CRT. In that case, it is convenient to display the treatment site, the position information, the size, the irradiation ultrasonic power and the time history of the treatment area which have been treated by the present method. Also, these information may be updated when a new treatment is performed. It should be noted that these pieces of information can be connected to a treatment planning device online or via a recording medium to assist the formulation of a treatment plan.

[0225]

The ultrasonic treatment apparatus according to the present invention comprises a therapeutic ultrasonic wave generation source having a resonance characteristic with respect to a first fundamental frequency, and an ultrasonic probe having a resonance characteristic with respect to a second fundamental frequency. Via the ultrasonic probe, means for driving the therapeutic ultrasonic wave generation source with the drive signal of the first fundamental frequency, means for driving the ultrasonic probe with the drive signal of the second fundamental frequency, Receiving means for receiving a first ultrasonic echo from the therapeutic ultrasonic generator and a second ultrasonic echo from the ultrasonic probe;
An intensity distribution configuring unit that configures an intensity distribution of the therapeutic ultrasonic wave based on a component of a specific band corresponding to the first fundamental frequency included in the received signal output from the receiving unit; and included in the received signal And a means for forming a tomographic image of the inside of the subject based on the component of the band including the second fundamental frequency.

The first ultrasonic wave transmitted for the intensity distribution is generated at the first fundamental frequency. The intensity distribution of the therapeutic ultrasonic wave is configured based on the component of the specific band corresponding to the first fundamental frequency included in the received signal. Therefore, the intensity distribution can be obtained with high accuracy. Further, the second ultrasonic wave transmitted for the tomographic image is generated at the second fundamental frequency. The tomographic image is configured based on the component of the band including the second fundamental frequency included in the received signal. Therefore, a tomographic image can be obtained with high accuracy. in this way,
The highly accurate intensity distribution and tomographic image realize improvement of safety and certainty of treatment.

The ultrasonic therapeutic apparatus according to the present invention comprises: a therapeutic ultrasonic wave generating source; an ultrasonic probe; and a therapeutic ultrasonic wave generating source for generating a first ultrasonic wave from the therapeutic ultrasonic wave generating source. A driving means for driving the source; and an adjusting means for adjusting a driving condition of the driving means based on the echo of the first ultrasonic wave received via the ultrasonic probe.

The drive condition for the therapeutic ultrasonic wave generation source is adjusted based on the echo of the first ultrasonic wave generated from the therapeutic ultrasonic wave generation source. This adjustment achieves improved safety and certainty of treatment.

[Brief description of the drawings]

FIG. 1 is a configuration diagram of an ultrasonic therapeutic apparatus according to a first embodiment.

FIG. 2 is a block diagram of the improved ultrasonic diagnostic unit of FIG.

FIG. 3 is a diagram showing a propagation path of ultrasonic waves.

FIG. 4 is a diagram showing a time difference between the timing of the ultrasonic pulse for imaging and the timing of the ultrasonic pulse for intensity distribution.

FIG. 5 is a configuration diagram of an ultrasonic therapeutic apparatus according to a second embodiment.

FIG. 6 is a configuration diagram of an ultrasonic therapeutic apparatus according to a third embodiment.

7 is a block diagram of the ultrasonic diagnostic unit of FIG.

FIG. 8 is a diagram showing a spectrum of a received signal.

9 is a diagram showing a display screen of the CRT shown in FIG.

FIG. 10 is a configuration diagram of an ultrasonic therapeutic apparatus according to a fourth embodiment.

FIG. 11 is a diagram showing a shift band due to blood flow.

FIG. 12 is a configuration diagram of an ultrasonic therapeutic apparatus according to a fifth embodiment.

FIG. 13 is a schematic structural diagram of a therapeutic ultrasonic wave generation source.

FIG. 14 is a diagram showing a high frequency band.

FIG. 15 is a diagram showing a deviation between a recognized focus and an estimated heat generation area.

FIG. 16 is a diagram showing a focus marker and a heat generation area marker.

FIG. 17 is a configuration diagram of an ultrasonic therapeutic apparatus according to a sixth embodiment.

FIG. 18 is a diagram showing a change in deviation between a calculated focal position and an actual focal position in the phased array technique.

FIG. 19 is a configuration diagram of an ultrasonic therapeutic apparatus according to a seventh embodiment.

FIG. 20 is an explanatory diagram of a problem solved by the ultrasonic therapy apparatus according to the eighth embodiment.

FIG. 21 is a diagram showing a temporal relationship between a therapeutic ultrasonic pulse and a scan for imaging.

22 is an explanatory diagram of a first method for solving the problem of FIG. 20. FIG.

23 is an explanatory diagram of a second method for solving the problem of FIG.

24 is an explanatory diagram of a third method for solving the problem of FIG.

25 is an explanatory diagram of a third method for solving the problem of FIG.

FIG. 26 is an explanatory diagram of a fourth method for solving the problem of FIG. 20.

FIG. 27 is a configuration diagram of an ultrasonic therapeutic apparatus according to a ninth embodiment.

FIG. 28 is a flowchart showing a processing procedure for determining an MRI slice.

29 is a diagram showing first and second scan planes of FIG. 28. FIG.

FIG. 30 is a supplementary explanatory diagram of detection of three-dimensional coordinates of a maximum intensity point.

FIG. 31 is a diagram showing an example of a combined screen of a B-mode image, peak temperature, and two-dimensional temperature distribution.

FIG. 32 is a time chart showing a series of processing flows from determination of MRI slices to the end of treatment.

FIG. 33 is a diagram showing an example of a combined display screen of a B-mode image, a peak temperature, and a one-dimensional temperature distribution.

FIG. 34 is a diagram showing a pulse sequence of MRI for obtaining a one-dimensional temperature distribution.

FIG. 35 is a flowchart showing a processing procedure for estimating a two-dimensional temperature distribution from a one-dimensional temperature distribution.

FIG. 36 is an explanatory diagram of real-time control of irradiation conditions by comparing the actually measured temperature distribution with the temperature distribution expected from the irradiation conditions.

FIG. 37 is a configuration diagram of an ultrasonic wave irradiation device according to a tenth embodiment.

38 is a block diagram of the phase shift circuit of FIG. 37.

FIG. 39 is an explanatory diagram of phase shift of a synchronization signal.

FIG. 40 is a configuration diagram of an ultrasonic wave irradiation device according to an eleventh embodiment.

41 is a diagram showing frequency characteristics of the quadrature detection circuit of FIG. 40.

FIG. 42 is a diagram showing a modification of FIG. 40.

FIG. 43 is a flowchart showing a procedure for determining the driving frequency of ultrasonic waves for intensity distribution.

FIG. 44 is a diagram showing a driving frequency of a therapeutic ultrasonic wave generation source.

FIG. 45 is a flowchart showing a procedure of a received frequency search process.

FIG. 46 is a configuration diagram of an ultrasonic wave irradiation device according to a twelfth embodiment.

47 is a diagram showing an example of a display screen of the display means of FIG. 46.

FIG. 48 is an explanatory view of the principle of causing a spatial mismatch between the B-mode image and the intensity distribution.

FIG. 49 is a configuration diagram of an ultrasonic wave irradiation device according to a thirteenth embodiment.

FIG. 50 is an explanatory diagram of adjustment of generation timing of ultrasonic waves for intensity distribution and generation timing of ultrasonic waves for imaging.

51 is a diagram showing another example of the display screen of the display means of FIG. 46.

FIG. 52 is an explanatory diagram of image reconstruction regarding a plane orthogonal to a scan plane of imaging.

[Explanation of symbols]

 1 ... Applicator, 2 ... Treatment ultrasonic wave generation source, 3 ... Patient, 4 ... Coupling liquid, 5 ... Water bag, 6 ... Body surface, 7 ... Treatment object, 8 ... Focus, 9 ... System controller, 10 ... console, 11 ... continuous generation circuit, 12 ... pulse generation circuit, 13 ... changeover switch, 14 ... RF amplifier, 15 ... matching circuit, 16 ... ultrasonic probe for imaging, 17 ... transmission circuit, 18 ... synchronization circuit, 19 ... Preamplifier, 20 ... Reception delay circuit, 21 ... Echo filter, 22 ... B mode processing unit, 27 ... Pulse Doppler unit, 28 ... Digital scan converter, 29 ... CRT.

 ─────────────────────────────────────────────────── ─── Continuation of the front page (72) Takuji Suzuki, Komukai-shi Toshiba Town, Saiwai-ku, Kawasaki-shi, Kanagawa 1 R & D Center, Toshiba Corporation (72) Satoshi Aida Satoshi Komukai, Saiwai-ku, Kawasaki-shi, Kanagawa Town No. 1 Toshiba Corporation Research & Development Center

Claims (16)

[Claims] 1. A therapeutic ultrasonic wave generation source having a resonance characteristic with respect to a first fundamental frequency, and an ultrasonic probe having a resonance characteristic with respect to the first fundamental frequency and a second fundamental frequency, Through a means for driving the therapeutic ultrasonic wave generation source with a drive signal of the first fundamental frequency, a means for driving the ultrasonic probe with a drive signal of the second fundamental frequency, and via the ultrasonic probe Receiving means for receiving an echo of the first ultrasonic wave from the ultrasonic source for treatment and an echo of the second ultrasonic wave from the ultrasonic probe, and based on a reception signal output from the receiving means An ultrasonic therapy apparatus comprising: a constituent unit that configures at least one of an intensity distribution of the therapeutic ultrasonic wave in the subject and a tomographic image in the subject. 2. A therapeutic ultrasonic wave generation source having a resonance characteristic with respect to a first fundamental frequency, an ultrasonic probe having a resonance characteristic with respect to a second fundamental frequency, and driving of the first fundamental frequency. A unit for driving the therapeutic ultrasonic wave generation source with a signal; a unit for driving the ultrasonic wave probe with a driving signal of the second fundamental frequency; Receiving means for receiving an echo of the first ultrasonic wave and an echo of the second ultrasonic wave from the ultrasonic probe, and the first fundamental frequency included in the reception signal output from the receiving means. An intensity distribution configuring unit that configures an intensity distribution of the therapeutic ultrasonic wave based on a component of a specified specific band, and an inside of the subject based on a component of a band including the second fundamental frequency included in the received signal Compose a tomographic image An ultrasonic treatment device comprising: 3. The specific band is at least one of a low frequency band including the first fundamental frequency and a high frequency band including a frequency that is an integral multiple of the first fundamental frequency. 2. The ultrasonic therapeutic device according to 2. 4. The intensity distribution forming means comprises means for analyzing the spectrum of the received signal and determining the specific band based on the frequency of the highest energy density. Sound wave therapy device. 5. The ultrasonic therapeutic apparatus according to claim 2, wherein the intensity distribution forming means has means for removing a blood flow component accompanied by frequency shift from the received signal. 6. A therapeutic ultrasonic wave generation source, an ultrasonic probe, and driving means for driving the therapeutic ultrasonic wave generation source to generate a first ultrasonic wave from the therapeutic ultrasonic wave generation source. And an adjusting unit that adjusts a driving condition of the driving unit based on an echo of the first ultrasonic wave received via the ultrasonic probe. 7. The adjusting means adjusts at least one of an amplitude of a drive signal input from the drive means to the therapeutic ultrasonic wave generation source and a duration of the drive signal. Item 6. The ultrasonic therapy device according to Item 6. 8. The ultrasonic therapy according to claim 6, wherein the adjusting unit adjusts the driving condition of the driving unit based on at least one of the amplitude of the echo and the energy corresponding to a specific band. apparatus. 9. The ultrasonic therapeutic apparatus according to claim 6, further comprising a constituent means for forming at least one of an intensity distribution and a tomographic image based on a reception signal output from the ultrasonic probe. 10. A therapeutic ultrasonic source, drive means for driving the therapeutic ultrasonic source to generate a therapeutic ultrasonic wave from the therapeutic ultrasonic source, and the therapeutic ultrasonic wave. An ultrasonic therapy apparatus comprising: a magnetic resonance diagnostic apparatus that measures a temperature distribution near a focal point at which the laser beam is focused; 11. A therapeutic ultrasonic wave generation source, an ultrasonic probe, and driving means for driving the therapeutic ultrasonic wave generation source to generate a first ultrasonic wave from the therapeutic ultrasonic wave generation source. A component for configuring an intensity distribution of the first ultrasonic wave based on an echo of the first ultrasonic wave received via the ultrasonic probe; and a magnetic resonance diagnostic apparatus for measuring a one-dimensional temperature distribution. An ultrasonic treatment apparatus comprising: an estimation unit that estimates a two-dimensional temperature distribution based on the intensity distribution and the one-dimensional temperature distribution. 12. A therapeutic ultrasonic wave generation source, an ultrasonic probe, a synchronizing signal generating means for generating a first synchronizing signal and a second synchronizing signal, and the medical treatment in accordance with the first synchronizing signal. Means for driving an ultrasonic wave generation source, means for driving the ultrasonic probe according to the second synchronization signal, and changing a time difference between the first synchronization signal and the second synchronization signal with time. By means of a phase shift means for giving a phase difference to the echo of the therapeutic ultrasonic wave, a first ultrasonic echo from the therapeutic ultrasonic wave generation source via the ultrasonic probe, and a first ultrasonic wave from the ultrasonic probe. A second receiving unit for receiving the echo of the ultrasonic wave, and a forming unit for forming an image based on the received signal phase-shifted by the phase-shifting unit repeatedly output from the receiving unit. Super sound Therapy device. 13. A therapeutic ultrasonic wave generation source, an ultrasonic probe, first driving means for driving the therapeutic ultrasonic wave source to generate the therapeutic ultrasonic wave, and an imaging ultrasonic wave. A second drive means for driving the ultrasonic probe, an echo of the first ultrasonic wave from the therapeutic ultrasonic wave generation source received via the ultrasonic probe, and a second ultrasonic wave from the ultrasonic probe. 2 means for forming an intensity distribution of the therapeutic ultrasonic wave and a tomographic image within the subject based on the echo of the ultrasonic wave; and means for estimating a treatment area that generates heat above a predetermined temperature based on the intensity distribution. An ultrasonic therapy device comprising: 14. The ultrasonic therapeutic apparatus according to claim 13, wherein the estimating unit estimates the treatment area by correcting at least one of the position and the size of the focus area on the intensity distribution. . 15. The ultrasonic therapeutic apparatus according to claim 13, further comprising means for displaying a marker representing the treatment region on the intensity distribution or the tomographic image. 16. At least one of an amplitude of a drive signal supplied from the first drive means to the therapeutic ultrasonic wave generation source, a duration of the drive signal, and a peak intensity in the intensity distribution. 14. The ultrasonic treatment apparatus according to claim 13, further comprising display means.