CN110141270A - Beam synthesizing method and equipment - Google Patents
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Abstract
The embodiment of the present invention provides a kind of beam synthesizing method and equipment.This method is applied to medical supersonic equipment, which includes hardware programmable logical device and processor.This method comprises: hardware programmable logical device obtains signal to be processed, signal to be processed is that the echo-signal that medical supersonic equipment interconnection receives carries out pretreated signal；Hardware programmable logical device carries out the sparse processing of signal to signal to be processed, and data are transferred to processor by treated；Processor carries out interpolation processing to the data received, and carries out Beam synthesis to the data after interpolation.The embodiment of the present invention can simply, conveniently, accurately realize Beam synthesis.
Description
Technical Field
The embodiment of the invention relates to a medical ultrasonic diagnosis technology, in particular to a beam forming method and device.
Background
In medical ultrasonic diagnostic technology, the most important part is beam forming, and the key of beam forming is the time delay calculation of data at different depths of different channels. Because the data intervals at different depths are very small, and the magnitude is tens of micrometers, the data volume is very large, and the large data volume cannot be transmitted to the processor in real time through the existing hardware transmission interface for beam synthesis, so that mainstream ultrasound equipment manufacturers adopt hardware programmable logic devices for beam synthesis.
However, beam forming by using hardware programmable logic is complex, and involves logic such as clock, etc., which makes deployment difficult. Therefore, there is a need for a simple, convenient and highly accurate beamforming scheme.
Disclosure of Invention
The embodiment of the invention provides a beam forming method and device, which can simply, conveniently and accurately realize beam forming.
In a first aspect, an embodiment of the present invention provides a beam forming method, which is applied to medical ultrasound equipment, where the medical ultrasound equipment includes a hardware programmable logic device and a processor. The method comprises the following steps:
the method comprises the steps that a hardware programmable logic device obtains a signal to be processed, wherein the signal to be processed is a signal obtained by preprocessing a received echo signal by medical ultrasonic equipment;
the hardware programmable logic device performs signal sparse processing on a signal to be processed and transmits the processed data to the processor;
the processor performs interpolation processing on the received data and performs beam forming on the interpolated data.
In a second aspect, an embodiment of the present invention provides a medical ultrasound apparatus, including:
the acquisition module is used for acquiring a signal to be processed, wherein the signal to be processed is a signal obtained by preprocessing a received echo signal by medical ultrasonic equipment;
the first processing module is used for performing signal sparse processing on the signal to be processed and transmitting the processed data to the second processing module;
and the second processing module is used for carrying out interpolation processing on the received data and carrying out beam forming on the interpolated data.
In a third aspect, an embodiment of the present invention provides a medical ultrasound apparatus, including:
the hardware programmable logic device is used for performing signal sparse processing on the acquired signal to be processed and transmitting the processed data to the processor, and the signal to be processed is a signal obtained by preprocessing the received echo signal by the medical ultrasonic equipment;
and the processor is used for carrying out interpolation processing on the received data and carrying out beam forming on the interpolated data.
In a fourth aspect, an embodiment of the present invention provides a readable storage medium, where a computer program is stored, and when the computer program is executed by a processor, the computer program implements the steps performed by the processor in the method according to the first aspect.
According to the beam forming method and device provided by the embodiment of the invention, the signal to be processed is obtained through the hardware programmable logic device, the signal to be processed is a signal obtained by preprocessing the received echo signal by the medical ultrasonic device, then the signal to be processed is subjected to signal sparse processing by the hardware programmable logic device, the processed data is transmitted to the processor, the processor performs interpolation processing on the received data, and beam forming is performed on the interpolated data. After the signal to be processed is subjected to signal sparse processing by the hardware programmable logic device, the processed data is transmitted to the processor, so that the data volume transmitted between the hardware programmable logic device and the processor in the medical ultrasonic equipment in real time is reduced, and beam forming can be realized by the processor through software; compared with the implementation mode of beam synthesis realized by a hardware programmable logic device, the processor can realize beam synthesis simply, conveniently and accurately.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, a brief description will be given below of the drawings required for the embodiments or the technical solutions in the prior art, and it is obvious that the drawings in the following description are some embodiments of the present invention, and other drawings can be obtained by those skilled in the art according to these drawings.
Fig. 1 is a flow chart of a beam forming method according to an embodiment of the present invention;
fig. 2 is a schematic diagram of signal changes in a beam forming method according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of a sampling process according to an embodiment of the present invention;
fig. 4 is a schematic diagram of related parameters such as an initial in-phase address according to an embodiment of the invention;
FIG. 5 is a diagram illustrating a multi-channel buffer according to an embodiment of the present invention;
fig. 6 is a flow chart illustrating a beam forming method according to another embodiment of the present invention;
fig. 7 is a schematic structural diagram of a medical ultrasound apparatus according to an embodiment of the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments of the present invention will be described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are some embodiments, but not all embodiments, of the present invention.
In the conventional beam forming, echo data of all channels need to be acquired by analog-to-digital converters (ADCs for short) with higher sampling rates, generally, the sampling rate of the ADCs is above 40MHz, the number of channels is 32, 48, 64, 128, etc., and each channel contains information of all sampling points in depth, so that such a large amount of data cannot be transmitted to a processor, such as a Central Processing Unit (CPU), in real time through an existing hardware transmission interface for beam forming. Because the multi-channel data is synthesized into one-line data after the beam synthesis is performed on the multi-channel high-sampling-rate digital signal, the data amount is greatly reduced, and the multi-channel data is uploaded to the processor end and can be transmitted in real time through a Universal Serial Bus (USB) 3.0 or a high-speed Serial computer extended Bus (PCIE) interface. In addition, when the hardware programmable logic device implements beam synthesis, initial parameters used for beam synthesis need to be stored, and meanwhile, the hardware programmable logic device needs to perform operations such as addition, subtraction, multiplication, division, evolution and the like in a beam synthesis algorithm formula, so that the operations and parameter storage greatly consume chip scarce resources such as a storage area and a multiplier of the hardware programmable logic device. No matter how much the optimized hardware programmable logic device realizes the beam synthesis, the method is only two in nature, wherein the hardware programmable logic device directly calculates the beam synthesis delay parameter, and the hardware programmable logic device indirectly calculates the beam synthesis delay parameter in an iterative mode by adopting the precomputation initial parameter, and the two modes can not avoid the participation of the hardware programmable logic device in the synthesis operation of multi-channel data. Therefore, how to reduce the implementation expense of the beam synthesis of the hardware programmable logic device or avoid using a hardware chip to implement the beam synthesis is of great importance to the whole medical ultrasonic equipment engineering.
Based on the above, embodiments of the present invention provide a beam synthesis method and device, which implement beam synthesis through software, avoid all operations such as addition, subtraction, multiplication, division, evolution and the like in a hardware implementation beam synthesis algorithm, and implement beam synthesis simply and conveniently.
Fig. 1 is a flowchart of a beam forming method according to an embodiment of the present invention. The embodiment of the invention provides a beam forming method, which is applied to medical ultrasonic equipment, wherein the medical ultrasonic equipment comprises a hardware programmable logic device and a processor.
As shown in fig. 1, the method includes:
s101, the hardware programmable logic device obtains a signal to be processed.
The signal to be processed is a signal obtained by preprocessing the received echo signal by the medical ultrasonic equipment.
In practical applications, a medical ultrasound apparatus, such as a color ultrasound apparatus, transmits an ultrasound signal to a subject, the ultrasound signal is reflected when encountering an obstacle (i.e., the subject), and a signal received by the color ultrasound apparatus is an echo signal.
It is to be understood that preprocessing herein refers to conventional processing, such as analog amplification, digital sampling, and the like. Optionally, the medical ultrasound device further includes an amplifier and a sampler, so that the hardware programmable logic device obtains the signal to be processed, which may specifically be: and the hardware programmable logic device acquires a signal to be processed output by the sampler through the high-speed serial port, wherein the signal to be processed is a signal obtained after an echo signal sequentially passes through the amplifier and the sampler. Illustratively, the sampler is an ADC, and the signal to be processed is a multi-channel high-frequency digital signal.
And S102, performing signal sparse processing on the signal to be processed by the hardware programmable logic device, and transmitting the processed data to the processor.
According to the analysis, the data volume of the signal to be processed is large, so that the signal to be processed is subjected to signal sparse processing through the hardware programmable logic device, and the data volume of the data transmitted to the processor by the hardware programmable logic device is reduced.
S103, the processor performs interpolation processing on the received data and performs beam forming on the interpolated data.
Considering that the accuracy of beam synthesis is related to the data rate, and the data obtained by the processor is the data subjected to signal thinning processing (the data rate of the data subjected to signal thinning processing is reduced compared with the signal to be processed), in this step, after the processor receives the data sent by the hardware programmable logic device, the data is firstly interpolated to recover the data rate, so that the accuracy of beam synthesis performed by the embodiment of the present invention is ensured, and beam synthesis can be quickly and conveniently realized by software without sacrificing the image quality.
According to the embodiment of the invention, a signal to be processed is obtained through a hardware programmable logic device, the signal to be processed is a signal obtained by preprocessing a received echo signal by medical ultrasonic equipment, then the signal to be processed is subjected to signal sparse processing by the hardware programmable logic device, the processed data is transmitted to a processor, the processor performs interpolation processing on the received data, and beam forming is performed on the interpolated data. After the signal to be processed is subjected to signal sparse processing by the hardware programmable logic device, the processed data is transmitted to the processor, so that the data volume transmitted between the hardware programmable logic device and the processor in the medical ultrasonic equipment in real time is reduced, and beam forming can be realized by the processor through software; compared with the implementation mode of beam synthesis realized by a hardware programmable logic device, the processor can realize beam synthesis simply, conveniently and accurately.
On the basis of the foregoing embodiment, in a specific implementation, the performing, by a hardware programmable logic device, signal sparseness on a signal to be processed may include: the hardware programmable logic device carries out frequency reduction processing on a signal to be processed to obtain a frequency reduction complex signal; the hardware programmable logic device performs low-pass filtering processing on the frequency reduction complex signal to obtain a low-frequency signal; and the hardware programmable logic device samples the low-frequency signal to obtain the processed data. The hardware programmable logic device carries out frequency reduction processing and sampling processing on the acquired signals to be processed to acquire processed data, the data volume on the depth is greatly reduced on the basis of meeting the Nyquist theorem, so that the processed data can be directly transmitted to the processor through the internal bus, the processor carries out interpolation reduction on the processed data to the data rate before frequency reduction according to the sampling rate of the sampling processing, meanwhile, the point-by-point beam synthesis is realized on the whole domain, the beam synthesis precision is ensured, and the final ultrasonic image still keeps a high-quality image.
Illustratively, the signal to be processed is shown as 21 in fig. 2, with a center frequency of f0 (MHz); the down-converted complex signal is shown at 22 in fig. 2 and includes a high frequency portion Z2 (center frequency 2f0) and a low frequency portion Z1 (center frequency 0). Where the down-conversion frequency is f0, low pass filtering, shown as 23 in fig. 2, removes the high frequency residual component and leaves the low frequency portion Z1, i.e. the low frequency signal. Referring to fig. 3, the low frequency signal 31 is sampled to obtain processed data 32.
It should be noted that the sampling rate of the sampling process is determined according to the density of the data to be processed. Fig. 3 illustrates a sample rate of 2, but the embodiment of the present invention is not limited thereto. Alternatively, the greater the data rate (density) of the data to be processed, the greater the sampling rate; the smaller the data rate of the data to be processed, the smaller the sampling rate.
In order to keep the data rate of the data beamformed by the processor to be the same as the data rate of the data to be processed, the processor performs interpolation processing on the received data, and the interpolation processing may include: the processor performs interpolation processing on the received data based on the sampling rate of the sampling processing, thereby ensuring the accuracy of beam forming.
Further, the beamforming the interpolated data by the processor may include:
1) aiming at the interpolated data corresponding to each channel, the processor performs the following processing:
A. calculating initial same-phase addresses of data at all depths in a channel;
B. acquiring anti-phase correction information corresponding to data at each depth in a channel according to the initial in-phase address and a frequency reduction frequency, wherein the frequency reduction frequency is a frequency corresponding to frequency reduction processing;
C. according to the anti-phase correction information, carrying out anti-phase correction on the interpolated data corresponding to the channel;
D. and acquiring final corrected data corresponding to the channel according to the decimal part and the integer part of the initial same-phase address and the data after the reverse phase correction.
2) And acquiring multi-channel synthesized beam data according to the final corrected data and the weighting coefficient corresponding to each channel.
Wherein, the weighting coefficients corresponding to different channels are the same or different.
In some embodiments, calculating the initial in-phase address of the data at each depth in the channel may include: and obtaining the initial same-phase address of the data at each depth in the channel according to the depth of each data in the channel, the sampling rate of sampling processing, the receiving delay point increment x-direction component, the receiving delay point increment y-direction component, the channel x-direction component, the channel y-direction component, the starting position x-direction component of the synthesized beam, the starting position y-direction component of the synthesized beam, the sampling rate corresponding to the signal to be processed and the sound velocity.
For example, as shown in FIG. 4, the initial in-phase address of the data at each depth in the channel is denoted as 52, which can be obtained by the following equation:
wherein:
i represents a channel number;
fs represents a sampling rate (MHz) corresponding to the signal to be processed;
vsound represents the corresponding sound velocity (m/s) of the signal to be processed;
d represents the depth of each data in the channel, as shown at 54 in FIG. 4;
m represents the sampling rate of the sampling process, as indicated at 57 in FIG. 4;
Δ x represents the reception delay time point increment x-direction component, as shown at 55 in fig. 4;
Δ y represents the reception delay time increment y-direction component, as shown at 56 in fig. 4;
chx (i) denotes the x-direction component of each channel, shown at 51 in fig. 4;
chy (i) denotes the y-direction component of each channel, as shown at 51 in FIG. 4;
beamx represents the x-direction component of the location of the origin of the synthesized beam, indicated at 53 in fig. 4;
beamy represents the y-direction component of the location of the origin of the synthesized beam, indicated at 53 in fig. 4;
the synthesized beam is shown at 58 in fig. 4.
B. According to the initial same-phase address and the frequency reduction, obtaining the anti-phase correction information corresponding to the data at each depth in the channel, which may specifically be:
wherein:
representing anti-phase correction information;
n-1 represents the maximum channel number;
f0 denotes the down frequency.
C. According to the inverse phase correction information, inverse phase correction is performed on the interpolated data corresponding to the channel, which may specifically be:
Z2_update(i,d)＝[Real(i,d)*cosφ(i,d)-Img(i,d)*sinφ(i,d)]
+[Real(i,d)*sinφ(i,d)+Img(i,d)*cosφ(i,d)]*j
wherein: z2_ update (i, d) represents the data after the inverse phase correction;
real (i, d) represents the Real part of the interpolated data;
img (i, d) denotes the imaginary part of the interpolated data.
D. According to the decimal part and the integer part of the initial same-phase address and the data after the reverse phase correction, the final corrected data corresponding to the channel is obtained, which may specifically be:
Z2_Fine(i,d)＝Fine_Address(i,d)*Z2_update(i,Coarse_Address(i,d))+
(1-Fine_Address(i,d))*Z2_update(i,Coarse_Address(i,d
wherein:
coarse _ Address (i, d) represents the integer part of the initial in-phase Address:
Coarse_Address(i,d)＝floor(Address_Inital(i,d))
fine _ Address (i, d) represents the fractional part of the initial in-phase Address:
Fine_Address(i,d)＝Address_Inital(i,d)-Coarse_Address(i,d)
floor denotes a downward integer;
z2_ Fine (i, d) represents the final rectified data for channel i.
2) Obtaining multi-channel synthesized beam data according to the final corrected data and the weighting coefficient corresponding to each channel, which may specifically be:
wherein:
coef (i) represents the weighting coefficient of channel i;
bf (d) represents the multi-channel synthesized beam data;
representing the notation operation symbol.
And acquiring digital signals of different channels according to the same-phase address and accumulating to acquire beam data of a certain sampling point on the universe. And the same-phase data of different sampling points in the depth domain are processed in parallel to quickly obtain the beam data of all the sampling points in the universe.
In some embodiments, the S102, performing signal sparsity processing on the signal to be processed by the hardware programmable logic device, and transmitting the processed data to the processor, may include: the hardware programmable logic device conducts signal sparse processing on the signals to be processed to obtain sparse data; the hardware programmable logic device carries out global multichannel caching on the sparse data to obtain global multichannel data; the hardware programmable logic device transmits the universe multi-channel data to the processor through the internal bus. The multi-channel buffer area for global multi-channel buffering of sparse data is preset, as shown in fig. 5.
Referring to fig. 6, the whole process of beam forming by the medical ultrasound apparatus is shown. Specifically, a transducer of the medical ultrasonic apparatus transmits an ultrasonic signal to a subject, and the ultrasonic signal is reflected when encountering the subject to form an echo signal, which is received by the transducer. The transducer then passes the echo signal to an amplifier, which performs analog amplification. Further, the amplifier transmits the amplified signal to the ADC, the ADC performs digital sampling processing, the sampled signal is transmitted to the hardware programmable logic device through a high-speed serial port, and the hardware programmable logic device performs sparse processing and caching, wherein the sparse processing includes but is not limited to frequency reduction processing, low-pass filtering processing and sampling processing. Then, the hardware programmable logic device transmits the data after sparse processing to the processor through an internal bus, and the processor performs beam forming: calculate in-phase address- > single point (sample point) beamforming- > global beamforming.
The following are embodiments of the apparatus of the present invention that may be used to perform embodiments of the method of the present invention. For details which are not disclosed in the embodiments of the apparatus of the present invention, reference is made to the embodiments of the method of the present invention.
Fig. 7 is a schematic structural diagram of a medical ultrasound apparatus according to an embodiment of the present invention. As shown in fig. 7, the present embodiment provides a medical ultrasound apparatus 70 including: an acquisition module 71, a first processing module 72 and a second processing module 73. Wherein,
an obtaining module 71, configured to obtain a signal to be processed. The signal to be processed is a signal obtained by preprocessing the received echo signal by the medical ultrasonic device 70.
The first processing module 72 is configured to perform signal sparseness on a signal to be processed, and transmit the processed data to the second processing module 73.
The second processing module 73 is configured to perform interpolation processing on the received data, and perform beam forming on the interpolated data.
The apparatus provided in the embodiment of the present invention may implement the technical solutions shown in the above method embodiments, and the implementation principles and beneficial effects thereof are similar, which are not described herein again.
Optionally, the first processing module 72 may be specifically configured to: performing frequency reduction processing on a signal to be processed to obtain a frequency reduction complex signal; low-pass filtering the frequency-reduced complex signal to obtain a low-frequency signal; and sampling the low-frequency signal to obtain the processed data. Alternatively, the sampling rate of the sampling process is determined according to the intensity of the data to be processed.
In some embodiments, the second processing module 73 may be specifically configured to: the received data is interpolated based on the sampling rate of the sampling process.
Further, when the second processing module 73 performs beamforming on the interpolated data, the beamforming may specifically be: for the interpolated data corresponding to each channel, the following processing is performed:
calculating initial same-phase addresses of data at all depths in a channel;
acquiring anti-phase correction information corresponding to data at each depth in a channel according to the initial in-phase address and a frequency reduction frequency, wherein the frequency reduction frequency is a frequency corresponding to frequency reduction processing;
according to the anti-phase correction information, carrying out anti-phase correction on the interpolated data corresponding to the channel;
acquiring final corrected data corresponding to the channel according to the decimal part and the integer part of the initial same-phase address and the data after the reverse phase correction;
and then, acquiring multi-channel synthesized beam data according to the final corrected data and the weighting coefficient corresponding to each channel. Wherein, the weighting coefficients corresponding to different channels are the same or different.
Optionally, when the second processing module 73 calculates the initial in-phase address of the data at each depth in the channel, it is specifically configured to: and obtaining the initial same-phase address of the data at each depth in the channel according to the depth of each data in the channel, the sampling rate of the sampling process, the receiving delay point increment x-direction component, the receiving delay point increment y-direction component, the channel x-direction component, the channel y-direction component, the starting position x-direction component of the synthesized beam, the starting position y-direction component of the synthesized beam, the sampling rate corresponding to the signal to be processed and the sound velocity.
Further, the first processing module 72 may be specifically configured to: performing signal sparse processing on a signal to be processed to obtain sparse data; carrying out global multichannel caching on the sparse data to obtain global multichannel data; and transmitting the global multichannel data to the processor through the internal bus.
Optionally, the medical ultrasound device 70 may further include an amplification module (not shown) and a sampling module (not shown). Wherein:
and the amplification module is used for carrying out analog amplification processing on the echo signals.
And the sampling module is used for performing digital sampling processing on the amplified signals and transmitting the sampled signals to the acquisition module 71 through a high-speed serial port.
Still referring to fig. 6, the present embodiment provides a medical ultrasound apparatus including: a hardware programmable logic device and a processor. Wherein,
and the hardware programmable logic device is used for performing signal sparse processing on the acquired signal to be processed and transmitting the processed data to the processor, wherein the signal to be processed is a signal obtained by preprocessing the received echo signal by the medical ultrasonic equipment.
And the processor is used for carrying out interpolation processing on the received data and carrying out beam forming on the interpolated data.
For specific implementation, reference may be made to any of the above method embodiments, which are not described herein again.
Embodiments of the present invention provide a readable storage medium, where a computer program is stored, and when the computer program is executed by a processor, the computer program implements steps performed by the processor in the method according to any of the above embodiments.
Those of ordinary skill in the art will understand that: all or a portion of the steps of implementing the above-described method embodiments may be performed by hardware associated with program instructions. The program may be stored in a computer-readable storage medium. When executed, the program performs steps comprising the method embodiments described above; and the aforementioned storage medium includes: various media that can store program codes, such as ROM, RAM, magnetic or optical disks.
Finally, it should be noted that: the above embodiments are only used for illustrating the technical solutions of the embodiments of the present invention, and are not limited thereto; although embodiments of the present invention have been described in detail with reference to the foregoing embodiments, those skilled in the art will understand that: the technical solutions described in the foregoing embodiments may still be modified, or some or all of the technical features may be equivalently replaced; and such modifications or substitutions do not depart from the spirit and scope of the embodiments of the present invention.
Claims (10)
1. A beamforming method applied to a medical ultrasound device, the medical ultrasound device comprising a hardware programmable logic device and a processor, the method comprising:
the hardware programmable logic device acquires a signal to be processed, wherein the signal to be processed is a signal obtained by preprocessing a received echo signal by the medical ultrasonic equipment;
the hardware programmable logic device performs signal sparse processing on the signal to be processed and transmits the processed data to the processor;
the processor performs interpolation processing on the received data and performs beam forming on the interpolated data.
2. The method of claim 1, wherein the hardware programmable logic device performs signal sparseness processing on the signal to be processed, and the method comprises:
the hardware programmable logic device carries out frequency reduction processing on the signal to be processed to obtain a frequency reduction complex signal;
the hardware programmable logic device carries out low-pass filtering processing on the frequency reduction complex signal to obtain a low-frequency signal;
and the hardware programmable logic device samples the low-frequency signal to obtain the processed data.
3. The method of claim 2, wherein the sampling rate of the sampling process is determined based on the intensity of the data to be processed.
4. The method of claim 2, wherein the processor interpolates the received data, comprising:
the processor interpolates the received data based on a sampling rate of the sampling process.
5. The method of claim 2, wherein the processor beamforms the interpolated data, comprising:
for the interpolated data corresponding to each channel, the processor performs the following processing:
calculating initial same-phase addresses of data at all depths in a channel;
acquiring anti-phase correction information corresponding to data at each depth in a channel according to the initial in-phase address and a frequency reduction frequency, wherein the frequency reduction frequency is a frequency corresponding to the frequency reduction processing;
according to the reverse phase correction information, reverse phase correction is carried out on the interpolated data corresponding to the channel;
acquiring final corrected data corresponding to a channel according to the decimal part and the integer part of the initial same-phase address and the data after reverse phase correction;
and obtaining multi-channel synthesized beam data according to the finally corrected data and the weighting coefficients corresponding to each channel, wherein the weighting coefficients corresponding to different channels are the same or different.
6. The method of claim 5, wherein calculating the initial in-phase address of the data at each depth in the channel comprises:
and obtaining the initial same-phase address of the data at each depth in the channel according to the depth (d) of each data in the channel, the sampling rate (M) of the sampling process, the receiving delay point increment x-direction component, the receiving delay point increment y-direction component, the channel x-direction component, the channel y-direction component, the starting position x-direction component of the synthesized beam, the starting position y-direction component of the synthesized beam, the sampling rate corresponding to the signal to be processed and the sound velocity.
7. The method of claim 1, wherein the hardware programmable logic device performs signal thinning on the signal to be processed and transmits processed data to the processor, and the method comprises:
the hardware programmable logic device performs signal sparse processing on the signal to be processed to obtain sparse data;
the hardware programmable logic device carries out global multichannel caching on the sparse data to obtain global multichannel data;
and the hardware programmable logic device transmits the global multichannel data to the processor through an internal bus.
8. The method of any one of claims 1 to 7, wherein the medical ultrasound device further comprises an amplifier and a sampler, and the hardware programmable logic device acquires the signal to be processed, comprising:
the hardware programmable logic device obtains the signal to be processed output by the sampler through a high-speed serial port, wherein the signal to be processed is obtained after the echo signal sequentially passes through the amplifier and the sampler.
9. A medical ultrasound device, comprising:
the acquisition module is used for acquiring a signal to be processed, wherein the signal to be processed is a signal obtained by preprocessing a received echo signal by the medical ultrasonic equipment;
the first processing module is used for performing signal sparse processing on the signal to be processed and transmitting the processed data to the second processing module;
the second processing module is used for carrying out interpolation processing on the received data and carrying out beam forming on the interpolated data.
10. A medical ultrasound device, comprising:
the hardware programmable logic device is used for performing signal sparse processing on the acquired signal to be processed and transmitting the processed data to the processor, wherein the signal to be processed is a signal obtained by preprocessing the received echo signal by the medical ultrasonic equipment;
the processor is used for carrying out interpolation processing on the received data and carrying out beam forming on the interpolated data.
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| CN109350112A (en) * | 2018-11-13 | 2019-02-19 | 飞依诺科技(苏州)有限公司 | Ultrasonic image imaging method and device and medical equipment |
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