JPH11328A - Ultrasonic diagnostic device and method for transmitting and receiving ultrasonic wave for ultrasonic diagnosis - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ultrasonic diagnostic device capable of efficiently suppressing grating lobe by controlling frequencies and bandwidths according to deflection angles at transmitting and receiving systems without giving rise to the problems of a high cost and heating, or reducing resolution in an area where the deflection angle is large and the distance over which a wave is received is long. SOLUTION: When the deflection angle of an ultrasonic beam is large, the pulse width of a driving pulse is increased by a pulse adjustment circuit 12. Since the central frequency of a wave transmitted decreases and its bandwidth narrows, generation of grating lobe resulting from high frequency components is restrained. No expensive linear amplifier or the like is required. In a receiving system, when the deflection angle is large a dynamic-band-pass filter 24 reduces the gradient of the central frequency with respect to the distance over which the wave is received. A reduction of grating lobe in the short range and a reduction in the rate at which resolution decreases in the far range are achieved simultaneously.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic diagnostic apparatus for performing deflection scanning of an ultrasonic beam, and more particularly to an apparatus capable of efficiently reducing grating lobes. Further, the present invention relates to an ultrasonic transmission / reception method applied to such an ultrasonic diagnostic apparatus. The above deflection scanning includes so-called sector scanning.

[0002]

2. Description of the Related Art An ultrasonic diagnostic apparatus that transmits an ultrasonic pulse to a subject, receives ultrasonic waves reflected in the subject, processes the received waves, and obtains information on the subject is well known. The ultrasonic diagnostic apparatus is provided with an array probe in which a plurality of ultrasonic vibration elements (piezoelectric elements) are arranged. By appropriately delaying the drive timing and the reception timing of each piezoelectric element, an ultrasonic beam can be formed in a desired direction. Hereinafter, an angle between a line passing through the center of the array of the vibrating elements and perpendicular to the array direction and the direction of the ultrasonic beam is referred to as a “deflection angle θ”. Ultrasonic beam direction (deflection angle θ)
Is changed for each beam is called deflection scanning, and sector scanning is well known as deflection scanning.

In an ultrasonic diagnostic apparatus, a grating lobe may be generated in a direction determined by a pitch of a vibration element and an ultrasonic wavelength, separately from an ultrasonic beam (main lobe). When this grating lobe appears in the field of view, a virtual image is generated, and the image quality of the ultrasonic image is degraded. It is known that the grating lobe increases as the deflection angle | θ | of the ultrasonic beam increases.

FIG. 1 shows an example of a sector scanning type ultrasonic probe. The pitch between the vibrating elements is p. As described above, the angle between the line passing through the center of the array of the vibrating elements and the main lobe is the deflection angle θ. Assuming that the wavelength of the ultrasonic wave is λ, the grating lobe due to the deflection of the ultrasonic beam does not theoretically occur if the following condition is satisfied.

[0005]

From the above equation, the smaller the element pitch p and the larger the wavelength λ (the lower the frequency), the more the deflection angle | θ | Is smaller, the grating lobes are less likely to occur. But,
Reducing the element pitch p is limited by cost and the like. This is because it is necessary to increase the number of vibrating elements even with the same opening. Also, if the wavelength λ is increased, the resolution is reduced, so that the wavelength λ cannot be too large.

When the center frequency of the ultrasonic wave is f0, the wavelength λ
0 = (sound speed / f0), and the deflection angle | 0 |
Assuming that the element pitch p is set so that the condition (equal sign) of the above equation (1) is satisfied even when the angle becomes °, p = λ0 /
It becomes 2. However, pulsed ultrasound has a bandwidth. Therefore, in this setting, a grating lobe occurs due to a frequency component higher than f0 (λ is smaller than λ0). As the deflection angle | θ | increases, the grating lobe increases.

As a method for reducing the grating lobe, there is a method described in Japanese Patent Publication No. 1-48992. In this publication, a variable band pass filter (BPF) is provided in a receiving circuit system.
Is provided. By controlling the high and low cutoff frequencies of this filter, the center frequency and bandwidth are changed according to the deflection angle θ, and the higher the deflection angle | θ | Removed. In the example of FIG. 2, the center frequency is changed according to the deflection angle θ,
In the example of FIG. 3, the bandwidth is changed according to the deflection angle θ, and in the example of FIG. 4, both the center frequency and the bandwidth are changed.

As described above, the larger the deflection angle | θ |, the larger the grating lobe due to the higher frequency. In the above publication, the provision of the variable BPF removes high-frequency components in a wide range when the deflection angle | θ | is large, and therefore suppresses the grating lobe efficiently.

Further, in the device disclosed in the above publication, it is proposed that the same principle is applied to the transmitting side, a variable BPF is provided in the transmitting circuit system, and the center frequency and the bandwidth of the variable BPF are controlled.

[0010]

However, the above-described prior art has the following problems in the case where the deflection angle adaptive variable BPF is provided on the transmission side and the reception side.

"Transmitting side" Generally, the voltage of the driving pulse supplied from the wave transmitting driver (or pulser) to the piezoelectric element is considerably high, for example, about 100V. Here, it is assumed that the variable BPF is applied before the transmission driver. In this case, the transmission driver needs to amplify the pulse after passing through the variable BPF to a high voltage while maintaining its waveform. To this end, the transmission driver must necessarily be provided with a linear high-voltage amplifier circuit. Such a linear amplifier circuit is expensive, and it is necessary to cope with heat generation of the transmission driver due to an increase in the amount of current.
On the other hand, it is assumed that the above-mentioned variable BPF is applied after the transmission driver (immediately before the piezoelectric element). Also in this case, a high voltage control circuit must be used, and heat generated due to a large amount of current must be dealt with. Thus, on the transmitting side, there is a disadvantage in providing the variable BPF itself.

[Receiving Side] Conventionally, it has been known that a receiving circuit system is provided with a dynamic BPF (distance adaptive type) for lowering the center frequency of a filter as the receiving distance increases, thereby improving the receiving efficiency and removing noise. ing. Here, the reception distance refers to a distance from a reflection point of the ultrasonic wave in the subject to the vibration element. For example, the above-described distance-adaptive dynamic BPF is realized by controlling the center frequency according to the return time of the ultrasonic wave. When the above-described deflection angle adaptive control is performed for the distance adaptive BPF, the following problem occurs.

A case where the center frequency is controlled as the deflection angle adaptive control will be considered. At this time, in a region where the deflection angle (absolute value) is large and the reception distance is long, the frequency reduction according to the deflection angle and the frequency reduction according to the reception distance overlap. as a result,
The center frequency of the filter is considerably reduced, and the azimuth resolution is reduced. The same applies to the case where the bandwidth of the filter is controlled as the deflection angle adaptive control. In a region where the deflection angle (absolute value) is large and the reception distance is long, the reduction of the distance resolution accompanying the reduction of the bandwidth becomes remarkable.

As described above, if the variable BPF for controlling the center frequency and the bandwidth in accordance with the deflection angle is provided, the grating lobe can be suppressed, but there is a disadvantage on both the transmitting side and the receiving side.

The present invention has been made in view of the above problems. Its purpose is to reduce the frequency and bandwidth according to the deflection angle in the transmission system and the reception system without causing the problem of high cost and heat generation, or without reducing the resolution in the region where the deflection angle is large and the reception distance is long. Is to provide an ultrasonic diagnostic apparatus capable of efficiently suppressing grating lobes by the above control. The present invention also provides an ultrasonic transmission / reception method for ultrasonic diagnosis capable of achieving the above object.

[0016]

[Means for Solving the Problems]

(1) An ultrasonic diagnostic apparatus according to the present invention includes: an array vibrator in which a plurality of ultrasonic vibrating elements are arranged; a scan control unit that performs ultrasonic beam deflection scanning by electronic scanning of the array vibrator; The driving pulse generator includes a driving pulse generator that generates a driving pulse for driving the vibrator and a pulse width control circuit that changes a pulse width of the driving pulse according to a deflection angle of the ultrasonic beam.

The principle of the present invention will be described with reference to FIGS. As the pulse width of the drive pulse applied to the array transducer is larger, the center frequency of the transmission wave is lower and the bandwidth is narrower. Therefore, as shown in FIGS. 5A and 5B, when the deflection angle | θ | is large, the pulse width of the driving pulse is increased (in FIG. 5B, the driving pulse has a rectangular waveform). Modeled). Thus, as shown in FIG. 6, the larger the deflection angle | θ |, the lower the center frequency of the transmission spectrum and the narrower the bandwidth. Therefore, the transmission spectrum is appropriately adjusted according to the deflection angle, and the grating lobe is suppressed.

As described above, according to the present invention, the pulse width control unit changes the pulse width of the drive pulse according to the deflection angle, and changes the center frequency and bandwidth of the transmission wave according to the pulse width. This effectively suppresses the grating lobe. Control of the pulse width can be realized by a circuit having a simple configuration. Amplification of the driving pulse can be realized by using an on-off type high voltage switching circuit having a simple configuration similar to the conventional one. Therefore, unlike the case where the variable BPF is provided in the transmission circuit system, there is no need to provide an expensive linear high-voltage amplifier circuit or a high-voltage control circuit, and there is no problem of heat generation by providing such a circuit. From the above, with a simple configuration,
It is possible to reduce the grating lobe at low cost and without the problem of heat generation, and to improve the image quality of a diagnostic image obtained by using an ultrasonic diagnostic apparatus.

In the present invention, it is preferable to provide a simple low-voltage circuit as a pulse width control circuit at a stage before the transmission driver. In addition, the pulse width control circuit can be provided at an arbitrary position before the array transducer. Also, it goes without saying that the pulse width control circuit may be integrated with the drive pulse generator within the scope of the present invention. In this case, the pulse width may be changed after the drive pulse is once generated, but the present invention also includes a configuration in which a drive pulse having a pulse width corresponding to the deflection angle is generated from the beginning.

In the example shown in FIG. 5, the pulse width is changed linearly as the deflection angle | θ | increases. On the other hand, the pulse width may change along a curve or may change stepwise, and may be changed to any form within the scope of the present invention.

(2) An ultrasonic diagnostic apparatus according to another aspect of the present invention performs an array transducer in which a plurality of ultrasonic transducers are arranged and deflects and scans an ultrasonic beam by electronic scanning of the array transducer. A scanning control unit, for driving the array transducer, a driving burst pulse generator that generates a driving burst pulse composed of a plurality of pulses, and a driving burst pulse between pulses of the driving burst pulse according to a deflection angle of the ultrasonic beam. A pulse interval control circuit for changing the period. The driving burst pulse is, for example, a driving signal including two or three pulses.

The principle of the present invention will be described with reference to FIGS. When a drive burst pulse composed of a plurality of pulses is given to the array transducer, the larger the period (interval) between the pulses, the lower the center frequency of the transmission wave and the narrower the bandwidth. Therefore, as shown in FIGS. 7A and 7B, when the deflection angle | θ | is large, the period between the pulses is increased (similar to FIG. 5B, in FIG. The waveform of the burst pulse is shown modeled in a rectangular shape). Even with this control, as shown in FIG. 6, the larger the deflection angle | θ |, the lower the center frequency of the transmission spectrum and the narrower the bandwidth. Therefore, the transmission spectrum is appropriately adjusted according to the deflection angle, and the grating lobe is suppressed.

As described above, according to the present invention, the pulse cycle of the drive burst pulse is changed by the pulse cycle interval control unit in accordance with the deflection angle, and the center frequency and the bandwidth of the transmission wave are changed. Grating lobes are effectively suppressed. Like the control of the pulse width, the control of the period of the pulse interval can be realized by a circuit having a simple configuration.
Further, the amplification of the driving burst pulse can be realized by using an on / off type high voltage switching circuit having a simple configuration similar to the conventional one. Therefore, similarly to the above mode (1), the grating lobe can be reduced with a simple configuration, at low cost, without generating heat, and the image quality of a diagnostic image obtained by using an ultrasonic diagnostic apparatus can be reduced. Can be increased.

Further, as in the above (1), it is preferable to provide a simple low-voltage circuit as a pulse interval control circuit at a stage before the transmission driver. In addition, the pulse interval control circuit can be provided at an arbitrary position before the array transducer. Also, the pulse interval control circuit is
Needless to say, it may be integrated with the drive pulse generator. In this case, the drive burst pulse may be generated once and then the pulse cycle may be changed. However, the present invention includes a configuration in which a drive burst pulse having a pulse cycle corresponding to the deflection angle is generated from the beginning.

In the example shown in FIG. 7, the pulse period is changed linearly as the deflection angle | θ | increases.
On the other hand, even if the pulse period changes along the curve,
It may change stepwise, and may be modified to any form within the scope of the present invention.

Further, according to the present invention, the pulse cycle of the driving burst pulse may be changed according to the deflection angle, and the pulse width of each pulse constituting the driving burst pulse may be changed according to the above-mentioned mode (1). .

(3) An ultrasonic diagnostic apparatus according to another aspect of the present invention performs an array transducer in which a plurality of ultrasonic transducers are arranged, and performs deflection scanning of an ultrasonic beam by electronic scanning of the array transducer. Including a scanning control unit. And the receiving system includes a deflection angle adaptive dynamic bandpass filter,
This filter has a frequency variable characteristic of filtering a received signal of each of the array vibrators and lowering a filtering center frequency when a reception distance is long. It is changed according to the deflection angle of the ultrasonic beam.

Preferably, the deflection angle adaptive type dynamic band-pass filter has a function of changing a frequency variable characteristic.
When the deflection angle of the ultrasonic beam is large, the gradient of the filtering center frequency with respect to the reception distance is reduced.

An ultrasonic diagnostic apparatus according to a preferred embodiment of the present invention comprises:
An array vibrator in which a plurality of ultrasonic vibrating elements are arranged, a scan control unit that performs ultrasonic beam deflection scanning by electronic scanning of the array vibrator, and a deflection angle adaptive dynamic band-pass filter, Filter the received signal of the array transducer, when the deflection angle of the ultrasonic beam is large, reduce the filtering center frequency, the difference of the center frequency according to this deflection angle,
The size decreases as the receiving distance increases.

The principle of the present invention will be described with reference to the example shown in FIG. FIG. 8A shows the filtering center frequency at each receiving distance in the deflection angle adaptive dynamic bandpass filter of the present invention for each deflection angle | θ |. FIG. 8B shows filter characteristics according to the deflection angle and the reception distance using a frequency spectrum.

In the conventional distance-adaptive dynamic band-pass filter (BPF), the center frequency is reduced when the receiving distance is long, as in the case where the deflection angle | θ | in FIG. 8 is small. Here, when the center frequency is reduced when the deflection angle is large in order to reduce the grating lobe, the center frequency becomes parallel (in parallel with the case where the deflection angle is small) in FIG.
Along the dotted line. As a result, in a region where the deflection angle | θ | is large and the reception distance is long, the center frequency is significantly reduced, and the azimuth resolution is reduced. This is a conventional problem.

The present invention focuses on the following points. Generally, the longer the reception distance (propagation distance) and the higher the frequency, the greater the amount of attenuation of the ultrasonic wave in the subject (frequency-dependent attenuation). Therefore, when the receiving distance is long, the amplitude of the high frequency component of the received wave becomes small, and the grating lobe becomes low. Focusing on this point, in the present invention, FIG.
As shown by the solid line in (a), when the deflection angle | θ | is large, the gradient of the center frequency with respect to the reception distance is reduced.

Therefore, at short distances, the difference in center frequency between when the deflection angle | θ | is small and when it is large is large. Thus, in a region where the deflection angle | θ | is large and the reception distance is short, the grating lobe is effectively reduced by removing the high-frequency component. On the other hand, at long distances, even if the deflection angle | θ | is large, the decrease in the azimuth resolution can be minimized by not reducing the center frequency so much. Even if the center frequency is not decreased, the amplitude of the high-frequency component of the received wave is small due to the above-described frequency-dependent attenuation, so that the grating lobe is low.

As described above, according to the present invention, the deflection angle | θ |
In this case, it is possible to effectively suppress the grating lobe while suppressing a decrease in resolution in a region where the reception distance is large and the reception distance is long. Therefore, an ultrasonic image with high image quality can be obtained in the entire region to be subjected to the deflection scanning.

In FIG. 8, the deflection angles | θ |
The center frequency for the small case is shown as a representative. In practice, of course, the center frequency may be continuously changed according to the deflection angle. In the example of FIG. 8, when the deflection angle | θ | is small at the longest reception distance,
Although the center frequency when the frequency is large is matched, it is needless to say that the center frequencies do not have to be matched in this way. Further, in FIG. 8, the center frequency is changed linearly as the receiving distance increases. On the other hand, the center frequency may change along a curve or may change stepwise. Further, when the deflection angle | θ | is large, the gradient of the center frequency with respect to the reception distance may be set to 0 (the decrease of the center frequency is set to 0). Further, the following control of the filtering bandwidth may be combined with the control of the center frequency as shown in FIG. As described above, specific control of the center frequency can be modified to any form within the scope of the present invention.

(4) An ultrasonic diagnostic apparatus according to another aspect of the present invention performs an array transducer in which a plurality of ultrasonic transducers are arranged, and performs deflection scanning of an ultrasonic beam by electronic scanning of the array transducer. A scanning controller and a deflection angle adaptive dynamic band pass filter are included. This filter is a dynamic band-pass filter having a frequency variable characteristic for filtering a reception signal of the array transducer and reducing a filtering center frequency when a reception distance is long, and a filtering band when a deflection angle of a reception beam is large. The width is narrowed, and the amount by which the bandwidth is narrowed at this time is changed according to the reception distance.

The principle of the present invention will be described with reference to the example shown in FIG. FIG. 9A shows the filtering bandwidth at each receiving distance in the deflection angle adaptive dynamic bandpass filter of the present invention for each deflection angle | θ |. FIG. 9B shows a filter characteristic according to the deflection angle and the reception distance.

The principle of this mode is almost the same as the principle of the mode (3) described with reference to FIG. By lowering the filtering center frequency according to the receiving distance and further narrowing the filtering bandwidth according to the deflection angle,
The resolution of the ultrasonic image is considerably reduced. Therefore, in the present invention, focusing on the above-described frequency-dependent attenuation, as shown in FIG. 9, the filter characteristics are controlled such that the difference according to the deflection angle of the filtering bandwidth becomes smaller as the receiving distance becomes longer. You.

Therefore, at short distances, the difference in filtering bandwidth between when the deflection angle | θ | is small and when it is large is large. Thus, in a region where the deflection angle | θ | is large and the reception distance is short, the grating lobe is effectively reduced by removing the high-frequency component. On the other hand, at long distances, even if the deflection angle | θ | is large, the reduction of the distance resolution can be minimized by not narrowing the filtering bandwidth too much. Even if the bandwidth is not reduced, the amplitude of the high-frequency component of the received wave is small due to the above-described frequency-dependent attenuation, so that the grating lobe is low.

As described above, according to the present invention, the above (3)
Similarly to the above, grating lobes can be effectively suppressed while suppressing a decrease in resolution in a region where the deflection angle | θ | is large and the reception distance is long. Therefore, an ultrasonic image with high image quality can be obtained in the entire region to be subjected to the deflection scanning.

In this embodiment, the above (3)
As in the embodiment described above, the filtering bandwidth may be changed continuously according to the deflection angle. Also, there is no need to match the bandwidths when the reception distance is long. Also, the center frequency and the bandwidth do not need to change linearly. When the deflection angle is small, the gradient of the bandwidth with respect to the reception distance may be zero. In addition, specific control of the filter characteristics can be modified to any form within the scope of the present invention.

(5) The ultrasonic transmitting method for ultrasonic diagnosis according to the present invention is a method of performing deflection scanning of an ultrasonic beam by electronic scanning of an array transducer in which a plurality of ultrasonic transducers are arranged. In this method, a drive signal consisting of a predetermined number of pulses for driving the array vibrator, the drive signal having a different pulse width or pulse interval depending on a deflection angle of the ultrasonic beam, is output from the array vibrator. Given to.

The number of pulses constituting the drive signal may be one. In this case, only the pulse width is changed according to the deflection angle. If the drive signal is composed of multiple pulses, depending on the deflection angle, even if only the pulse interval is changed,
Alternatively, only the pulse width of each pulse may be changed. Further, both the pulse interval and the pulse width may be changed according to the deflection angle. According to the present invention, as described with reference to FIGS. 5 to 7, the grating lobe can be efficiently reduced using a simple circuit configuration.

(6) An ultrasonic receiving method for ultrasonic diagnosis according to another aspect of the present invention is a method of performing deflection scanning of an ultrasonic beam by electronic scanning of an array transducer in which a plurality of ultrasonic transducers are arranged. It is. In this method, at the time of filtering the received signal using the band-pass filter, at least one of the center frequency and the bandwidth of the filtering is performed so that a high-frequency component of the received signal that generates a grating lobe is removed. It is changed according to the deflection angle and the reception distance of the reception signal.

As described above, when the receiving distance is long,
The amplitude of the high-frequency component of the received wave decreases, and the grating lobe decreases. Performing control of the center frequency and bandwidth according to the deflection angle even if the reception distance is long,
Not only is the grating lobe reduction effect small,
This leads to a decrease in azimuth resolution and distance resolution. According to the present invention, the center frequency and the bandwidth are changed at each position in the two-dimensional region specified by the deflection angle and the reception distance. Therefore, grating lobes can be effectively reduced while suppressing a decrease in azimuth resolution and distance resolution.

The filter used in this embodiment is not limited to a filter that lowers the center frequency as the receiving distance increases. For example, when the deflection angle is small, the center frequency is constant with respect to the change in the reception distance, and when the deflection angle is large, the center frequency is decreased as the reception distance becomes shorter. In addition, for example, there is a method in which the center frequency is always fixed, and the filtering bandwidth is changed according to the deflection angle and the reception distance.

[0047]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Preferred embodiments of the present invention (hereinafter, referred to as embodiments) will be described below with reference to the drawings. FIG. 10 is a block diagram illustrating an ultrasonic diagnostic apparatus according to the present embodiment. The array probe 1 is provided with a plurality of ultrasonic vibration elements arranged in an array. At the top of FIG.
The configuration of a transmission system for driving the array probe 1 is shown, and the lower part of FIG. 10 shows the configuration of a reception system for processing a signal received by the array probe 1. The control unit 3 controls the overall configuration of the transmission system and the reception system to form an ultrasonic beam. And the control part 3
The formation of the ultrasonic beam is repeated while sequentially changing the deflection angle. Thus, sector scanning using the array probe 1 is performed.

In the transmission system, the drive signal generator 10
The timing is controlled by the control unit 3 to generate a drive signal serving as a trigger for ultrasonic transmission. The drive signal generator 10 includes:
A drive signal is generated in one of two modes, a drive pulse mode and a drive burst pulse mode. In the drive pulse mode, one pulse is output as a drive signal for each transmission. In driving burst pulse mode,
A drive burst pulse composed of a plurality of pulses is output for each transmission. The number of drive burst pulses is set to about 2 to 4.

The drive signal generator 10 is connected to a pulse adjustment circuit 12 which is characteristic in this embodiment.
When the “drive pulse” is input, the pulse adjustment circuit 12
Adjusts the pulse width of the drive pulse. Pulse adjustment circuit 1
2 is controlled by the control unit 3. The control unit 3
According to FIG. 5, the pulse width is determined according to the deflection angle θ of the ultrasonic beam. That is, the larger the deflection angle | θ |
The pulse width is determined to be large. The control unit 3 issues an instruction (pulse width instruction) to the pulse adjustment circuit 12, and changes the pulse width of the drive pulse to the magnitude determined according to FIG.

When the "drive burst pulse" is input, the pulse adjusting circuit 12 adjusts the interval (cycle) between the drive burst pulses. At this time, the control unit 3
Determines the pulse interval according to the deflection angle θ according to FIG. That is, the larger the deflection angle | θ |, the larger the pulse interval is determined. The control unit 3 includes the pulse adjustment circuit 1
An instruction (pulse interval instruction) is issued to the control unit 2 to change the pulse width of the drive pulse to the size determined according to FIG.

The pulse adjusting circuit 12 is connected to a transmission beam forming circuit 14 and a transmission driver 16 having the same configuration as in the prior art. The transmission beam forming circuit 14 includes a delay circuit, and has a number of delay lines corresponding to the number of vibrating elements of the array probe 1. Information indicating the deflection angle θ is input from the control unit 3 to the transmission beam forming circuit 14. Based on this information, the transmission beam forming circuit 14 controls the delay amount (delay amount distribution) of each delay line so that a transmission beam is formed in the direction of the deflection angle θ. The drive signal delayed by each delay line is output to the transmission driver 16. The wave transmitting driver 16 is connected to each vibration element of the array probe 1. The wave transmission driver 16 amplifies the input drive signal to generate a high-voltage pulse signal, and outputs the amplified signal to each vibrating element of the array probe 1. Each of the vibrating elements is excited by this amplified signal and emits an ultrasonic wave. In this way, each of the vibrating elements emits an ultrasonic wave at a shifted timing, and a transmission beam is formed in the direction of the deflection angle θ.

Next, the configuration of the receiving system will be described. Ultrasonic waves emitted from the array probe 1 are reflected back inside the subject. The array probe 1 receives an ultrasonic wave, converts this ultrasonic signal into an electric signal, and outputs the electric signal. A receiving amplifier 20 for amplifying a received signal is connected to the array probe 1. The amplified reception signal is output to the reception beam forming circuit 22. The reception beam forming circuit 22 has the same configuration as that of the related art, and includes a phasing addition circuit. In the reception beam forming circuit 22, under the control of the control unit 3, the output signal of each vibrating element is delayed. Then, the received signals after the delay processing are added and combined into one signal.

The reception beam forming circuit 22 is connected to a deflection angle adaptive dynamic bandpass filter (hereinafter referred to as VDBPF) 24 which is characteristic of the present embodiment. V
The DBPF 24 is controlled by the control unit 3. The control unit 3 changes the filter characteristics of the VDBPF 24 according to FIG. 8 or FIG. To change the filter characteristics, the control unit 3 outputs a control signal for controlling the cutoff frequencies of the high band and the low band to the VDBPF 24. By controlling both cutoff frequencies, it is possible to change the center frequency and the pass bandwidth, which are filter characteristics.

When FIG. 8 is adopted, when the deflection angle | θ | is small, the gradient of the center frequency with respect to the reception distance is set large, and when the deflection angle | θ | is large, the gradient of the center frequency is reduced. Therefore, at short distances, the difference between the center frequencies when the deflection angles | θ |
According to this setting, the control unit 3 determines the cutoff frequency of the VDBPF 24. As is well known, the filter characteristic can be changed according to the reception distance by using the return time of the ultrasonic wave as a parameter.

When FIG. 9 is adopted, the bandwidth is controlled based on the reception distance. At the deflection angle θ = 0, the bandwidth is constant regardless of the length of the reception distance. When the deflection angle θ is other than 0, the bandwidth is set to be narrower as the receiving distance is shorter. The larger the deflection angle | θ |, the larger the gradient of the bandwidth with respect to the reception distance. Therefore, at a short distance, the difference in bandwidth when the deflection angle | θ | is different is large.

In the case where FIG. 9 is employed, the center frequency is set such that the longer the reception distance, the lower the center frequency. However, the control of the center frequency according to the magnitude of the deflection angle is not performed, and the center frequency is set to be the same regardless of whether the deflection angle is large or small.

The VDBPF 24 is connected to a compression detection circuit 26, an image processing circuit 28, and a display 30 having the same configuration as the conventional one. The compression detection circuit 26 extracts information in the subject from the received signal by processing such as detection. An image representing the information in the subject (B mode, M mode, etc.)
Is generated by the image processing circuit 28. The display 30 is a CRT
And the like, and the generated ultrasonic image is displayed.

The above operation of the ultrasonic diagnostic apparatus is referred to as "transmission".
And "Reception".

"Transmission" Here, a description will be given mainly of a case where transmission is performed using a drive pulse as a drive signal. The control unit 3 causes the drive signal generator 10 to generate a drive pulse having a predetermined pulse width. When the ultrasonic beam is formed in the direction of the deflection angle θ = 0, that is, in the direction of the front of the array probe 1, the drive pulse passes through the pulse adjustment circuit 12 as it is and is input to the transmission beam formation circuit 14. . The transmission beam forming circuit 14 delays the drive pulse so that a transmission beam is formed in the direction of the deflection angle θ = 0. The drive pulse is amplified by the transmission driver 16 and output to the array probe 1. Each vibrating element of the array probe 1 is excited at a slightly shifted timing and emits an ultrasonic wave. As a result, the deflection angle θ = 0
A transmission beam is formed in the direction of.

When forming a transmission beam in a direction other than the deflection angle θ = 0, the control unit 3 controls the pulse adjustment circuit 12 to change the pulse width of the drive pulse as shown in FIG. Using the drive pulse whose pulse width has been adjusted, the transmission beam forming circuit 14, the transmission driver 16, and the array probe 1 transmit ultrasonic waves, and a transmission beam is formed in the direction of the deflection angle θ. .

Here, as described above, the frequency range causing the grating lobe changes according to the deflection angle θ. When the deflection angle | θ | is large, lower frequency components also cause grating lobes. In the present embodiment, the greater the deflection angle | θ |, the larger the pulse width of the drive pulse. As shown in the transmission spectrum of FIG.
As the pulse width of the drive pulse is larger, the center frequency of the transmission beam generated using the drive pulse shifts downward, and the bandwidth of the transmission beam becomes narrower. Therefore, when a transmission beam is formed in the direction of each deflection angle θ, it is possible to transmit an ultrasonic wave that does not include a frequency component that causes a grating lobe to appear at the deflection angle θ.

In the above description, the transmission was performed using the driving pulse. The same applies when transmission is performed using a driving burst pulse. In this case, when forming a transmission beam in the direction of the deflection angle θ = 0, the drive burst pulse passes through the pulse adjustment circuit 12 as it is. When the deflection angle θ is other than 0, the pulse interval of the driving burst pulse is changed by the pulse adjustment circuit 12 in accordance with the setting in FIG. The larger the pulse interval, the lower the center frequency of the transmitted beam and the narrower the bandwidth. Therefore, similarly to the above, the grating lobe is efficiently suppressed.

[Reception] Here, the VDBPF 24
A description will be given mainly of a case where the filter characteristics are controlled in accordance with the settings in FIG.

When the array probe 1 receives the ultrasonic wave,
An electric signal corresponding to the intensity of the ultrasonic wave is output. The reception signal is amplified by the reception amplifier 20, and is subjected to delay processing and addition processing according to the deflection angle θ in the reception beam forming circuit 22. As a result, a reception beam is formed in the direction of the deflection angle θ.

The echo signal after the addition processing is VDBPF2
4 is input. The control unit 3 controls the center frequency of the echo signal passing through the VDBPF 24 in accordance with the settings shown in FIG. When the deflection angle | θ | is small, the center frequency decreases relatively significantly as the reception distance increases. That is, when the echo signal reflected at a deep point of the subject passes through the filter, the center frequency is lowered. Thereby, reception efficiency is improved and noise is effectively removed. Even when the deflection angle | θ | is large, the center frequency decreases as the reception distance increases. However, as the deflection angle | θ | increases, the gradient of the center frequency with respect to the reception distance decreases.

According to the setting in FIG. 8, when the receiving distance is short, the center frequency is changed to be lower as the deflection angle | θ | is larger. Therefore, when a reception beam is formed in the direction of each deflection angle, a frequency component that causes a grating lobe to appear at that deflection angle is efficiently removed.

When the receiving distance is long, the difference of the center frequency according to the deflection angle becomes small, and the center frequency becomes almost the same both when the deflection angle | θ | is large and small. However, when the receiving distance is long, the amplitude of the high-frequency component in the echo signal causing the grating lobe becomes small. Therefore, the grating lobe is small without lowering the center frequency. With this setting, the azimuth resolution in a region where the deflection angle | θ | is large and the reception distance is long can be obtained as much as that in a region where the deflection angle | θ | is small.

The echo signal that has passed through the VDBPF 24 is
The data is input to the compression detection circuit 26 and subjected to processing such as detection. Then, an image for display is generated from the signal after detection and displayed on the display 30. Since the grating lobes are suppressed in both transmission and reception, a good ultrasonic image without virtual images due to the grating lobes can be obtained.

The case where the setting of FIG. 8 is employed for controlling the filter characteristics of the VDBPF 24 has been described above. On the other hand, when the setting of FIG. 9 is adopted, the control of the center frequency according to the reception distance is performed similarly when the deflection angle | θ | is large or small. However, the bandwidth of the filter is controlled according to the deflection angle and the reception distance as shown in FIG. When the reception distance is short, the bandwidth is narrowed as the deflection angle increases, thereby suppressing the grating lobe. If the receiving distance is long,
The bandwidth is almost the same when the deflection angle | θ | is large or small. Even in this case, when the reception distance is long, the amplitude of the high-frequency component in the echo signal is small, so that the grating lobe is small. Then, the distance resolution in a region where the deflection angle | θ | is large and at a long distance can be obtained in the same range as the region where the deflection angle | θ | is small.

The ultrasonic diagnostic apparatus according to the present embodiment has been described. As a modification of the present embodiment, when a drive system generates a drive burst pulse, both the pulse width and the pulse interval may be changed according to the deflection angle θ. In the receiving system, the settings in FIGS. 8 and 9 may be combined. In this case, VD is adjusted so that both the center frequency and the bandwidth change according to the deflection angle and the receiving distance.
The BPF 24 is controlled.

[0071]

According to the present invention, by controlling the pulse width and the pulse interval of the drive signal, the center frequency and the bandwidth of the transmission wave change according to the deflection angle, and the grating lobe is efficiently suppressed. . The control of the pulse width and the pulse interval can be realized by a circuit having a simple configuration. Amplification of the pulse signal can be realized using an amplifier having a simple configuration.
Therefore, with a simple configuration, it is possible to reduce the grating lobe at low cost and without the problem of heat generation, and to enhance the image quality of a diagnostic image obtained by using the ultrasonic diagnostic apparatus.

According to the present invention, the center frequency and the bandwidth of the band-pass filter provided in the receiving system are controlled in accordance with the deflection angle of the ultrasonic beam to reduce the grating lobe. Therefore, it is possible to suppress a decrease in resolution in a region where the reception distance is large and the reception distance is long. Therefore, an ultrasonic image with high image quality can be obtained in the entire region to be subjected to the deflection scanning.

[Brief description of the drawings]

FIG. 1 is a diagram showing the definition of the deflection angle of an ultrasonic beam together with the arrangement of the transducers of an array probe.

FIG. 2 is a diagram illustrating an example of a technique for reducing a grating lobe by controlling a frequency spectrum according to a deflection angle of an ultrasonic beam.

FIG. 3 is a diagram illustrating an example of a technique for reducing a grating lobe by controlling a frequency spectrum according to a deflection angle of an ultrasonic beam.

FIG. 4 is a diagram illustrating an example of a technique for reducing a grating lobe by controlling a frequency spectrum according to a deflection angle of an ultrasonic beam.

FIG. 5 is a view showing the principle of the first embodiment of the present invention, showing setting of a pulse width of a driving pulse according to a deflection angle.

FIG. 6 is a diagram showing a change in a transmission spectrum under the control of FIG. 5;

FIG. 7 is a view showing the principle of the second embodiment of the present invention, showing the setting of the pulse cycle of the drive burst pulse according to the deflection angle.

FIG. 8 is a diagram illustrating setting of filter characteristics of a reception band-pass filter according to a reception distance and a deflection angle according to a principle of a third embodiment of the present invention.

FIG. 9 is a diagram illustrating setting of filter characteristics of a receiving band-pass filter according to a receiving distance and a deflection angle according to a principle of a fourth embodiment of the present invention.

FIG. 10 is a block diagram illustrating a configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention.

[Explanation of symbols]

Reference Signs List 1 array probe, 3 control unit, 10 drive signal generator, 12 pulse adjustment circuit, 14 transmission beam forming circuit, 16 transmission driver, 20 reception amplifier, 22 reception beam formation circuit, 24 deflection angle adaptive dynamic band Pass filter, 26 compression detection circuit, 28 image processing circuit, 30 display.

Claims (8)

[Claims] An array transducer in which a plurality of ultrasonic transducers are arranged; a scanning controller for performing deflection scanning of an ultrasonic beam by electronic scanning of the array transducer; and a drive unit for driving the array transducer. An ultrasonic diagnostic apparatus comprising: a driving pulse generator that generates a driving pulse; and a pulse width control circuit that changes a pulse width of the driving pulse according to a deflection angle of the ultrasonic beam. 2. An array vibrator in which a plurality of ultrasonic vibrating elements are arranged; a scan control unit for performing deflection scanning of an ultrasonic beam by electronic scanning of the array vibrator; and a driving unit for driving the array vibrator. A drive burst pulse generator that generates a drive burst pulse composed of a plurality of pulses, and a pulse interval control circuit that changes a period between pulses of the drive burst pulse according to a deflection angle of the ultrasonic beam. Ultrasound diagnostic device characterized by the following. 3. An array vibrator in which a plurality of ultrasonic vibrating elements are arranged; a scan controller for performing deflection scanning of an ultrasonic beam by electronic scanning of the array vibrator; and filtering a received signal of the array vibrator. When the reception distance is long, the filter has a frequency variable characteristic of lowering the filtering center frequency, and the deflection angle for changing the reduction width of the center frequency according to the reception distance in the frequency variable characteristic according to the deflection angle of the ultrasonic beam. An ultrasonic diagnostic apparatus comprising: an adaptive dynamic band-pass filter. 4. The apparatus according to claim 3, wherein the deflection angle adaptive dynamic band-pass filter is configured to change the frequency variable characteristic when the deflection angle of the ultrasonic beam is large and the filtering center frequency with respect to a reception distance. An ultrasonic diagnostic apparatus characterized in that the gradient of the ultrasound is reduced. 5. An array vibrator in which a plurality of ultrasonic vibrating elements are arranged; a scan control unit for performing deflection scanning of an ultrasonic beam by electronic scanning of the array vibrator; and filtering a received signal of the array vibrator. When the deflection angle of the ultrasonic beam is large, the filtering center frequency is lowered, and the difference between the center frequencies according to the deflection angle, a deflection angle adaptive dynamic bandpass filter that reduces as the receiving distance increases, An ultrasonic diagnostic apparatus comprising: 6. An array vibrator in which a plurality of ultrasonic vibrating elements are arranged; a scan control unit for performing deflection scanning of an ultrasonic beam by electronic scanning of the array vibrator; and filtering a reception signal of the array vibrator. A dynamic band-pass filter having a frequency variable characteristic that lowers the filtering center frequency when the reception distance is long. When the deflection angle of the reception beam is large, the filtering bandwidth is narrowed. And a deflection angle adaptive dynamic band-pass filter that varies according to the reception distance. 7. An ultrasonic transmission method for ultrasonic diagnosis, wherein an ultrasonic beam is deflected and scanned by electronic scanning of an array transducer in which a plurality of ultrasonic transducers are arranged. Ultrasound for ultrasonic diagnostics, comprising: providing a drive signal having a predetermined number of pulses to the array transducer, the drive signal having a different pulse width or a pulse interval according to a deflection angle of the ultrasonic beam. Transmission method. 8. An ultrasonic receiving method for ultrasonic diagnosis in which deflection scanning of an ultrasonic beam is performed by electronic scanning of an array vibrator in which a plurality of ultrasonic vibrating elements are arranged, wherein a reception signal is transmitted using a band-pass filter. At the time of filtering, at least one of the center frequency and the bandwidth of the filtering is changed according to the deflection angle of the ultrasonic beam and the reception distance of the reception signal so that the high-frequency component of the reception signal that generates the grating lobe is removed. An ultrasonic receiving method for ultrasonic diagnosis, comprising: