阅读说明：本技术 超声血流成像装置及超声设备 (Ultrasonic blood flow imaging device and ultrasonic equipment ) 是由 王鋐 曹三 杨成 张勇 于 2020-06-10 设计创作，主要内容包括：本发明涉及图像处理技术领域,具体涉及一种超声血流成像装置及超声设备。其中,超声血流成像装置包括：存储器和处理器,存储器中存储有至少一条程序指令,处理器通过加载并执行至少一条程序指令以实现如下步骤：通过交织发射接收的方式发射超声脉冲,接收n个回波信号,n为大于1的整数；获取n个回波信号的差分信号d(t)；对n个回波信号进行幅值检测,得到每个回波信号的包络线,获取各个回波信号的包络线的和B(t)；根据d(t)和B(t)计算血流成像模式的图像灰度强度；获取B模式超声回波数据；对B模式超声回波数据以及计算得到的血流成像模式的图像灰度强度进行扫描变换,根据转换结果显示超声图像。解决了现有技术中超声图像中存在伪影的问题。(The invention relates to the technical field of image processing, in particular to an ultrasonic blood flow imaging device and ultrasonic equipment. Wherein, supersound blood flow image device includes: the device comprises a memory and a processor, wherein at least one program instruction is stored in the memory, and the processor loads and executes the at least one program instruction to realize the following steps: transmitting ultrasonic pulses in an interleaving transmitting and receiving mode, and receiving n echo signals, wherein n is an integer greater than 1; acquiring differential signals d (t) of n echo signals; carrying out amplitude detection on the n echo signals to obtain an envelope curve of each echo signal, and obtaining the sum B (t) of the envelope curves of the echo signals; calculating the image gray scale intensity of the blood flow imaging mode according to d (t) and B (t); acquiring B-mode ultrasonic echo data; and carrying out scanning transformation on the B-mode ultrasonic echo data and the calculated image gray intensity of the blood flow imaging mode, and displaying the ultrasonic image according to the conversion result. The problem of there is the artifact in the ultrasonic image among the prior art is solved.)

1. An ultrasonic blood flow imaging apparatus, the apparatus comprising: a memory having at least one program instruction stored therein, and a processor that, upon loading and executing the at least one program instruction, performs the steps of:

transmitting ultrasonic pulses in an interleaving transmitting and receiving mode in a blood flow imaging mode, and receiving n echo signals, wherein n is an integer greater than 1;

acquiring differential signals d (t) of n echo signals;

carrying out amplitude detection on the n echo signals to obtain an envelope curve of each echo signal, and obtaining the sum B (t) of the envelope curves of the echo signals;

calculating image gray scale intensity of a blood flow imaging mode according to the d (t) and the B (t);

acquiring B-mode ultrasonic echo data;

and scanning and converting the B-mode ultrasonic echo data and the calculated image gray intensity of the blood flow imaging mode, and displaying an ultrasonic image according to a conversion result.

2. The apparatus of claim 1, wherein the transmitting ultrasound pulses by interleaving transmit and receive in a blood flow imaging mode comprises:

starting the transmitting and receiving of the jth group of receiving lines, wherein the starting value of j is 1;

and after the jth group of receiving lines is received, j +1 is carried out, and the step of starting the transmitting and receiving of the jth group of receiving lines is immediately executed.

3. The apparatus of claim 1, wherein said calculating an image gray scale intensity of a blood flow imaging mode from said d (t) and said b (t) comprises:

according to the B (t) and a preset threshold value N_tholdUpdating the value of B (t);

and calculating the image gray intensity of the blood flow imaging mode according to the d (t) and the updated B (t).

4. The apparatus according to claim 3, wherein said predetermined threshold N is set according to said B (t)_tholdUpdating the magnitude relationship of B (t)Numerical values, including:

if B (t)<N_tholdThen N will be_tholdAs updated b (t).

5. The apparatus of claim 3, wherein the calculating the image gray scale intensity of the blood flow imaging mode according to d (t) and the updated B (t) comprises:

the image gray scale intensity of the blood flow imaging mode is as follows:

alternatively, the first and second electrodes may be,

the image gray scale intensity of the blood flow imaging mode is as follows:

6. the apparatus of claim 1, wherein the scan converting the B-mode ultrasound echo data and the calculated image gray scale intensity of the blood flow imaging mode, and displaying the ultrasound image according to the conversion result comprises:

combining the B-mode ultrasonic echo data and the image of the blood flow imaging mode, and displaying the combined ultrasonic image;

alternatively, the first and second electrodes may be,

displaying a B mode ultrasonic image according to the B mode ultrasonic echo data; and displaying the blood flow image according to the image gray intensity of the blood flow imaging mode.

7. The apparatus of claim 6, wherein said combining the B-mode ultrasound echo data and the image of the blood flow imaging mode, displaying the combined ultrasound image, comprises:

and determining the brightness of the combined ultrasonic image according to the magnitude relation between the brightness of the image in the blood flow imaging mode and a brightness threshold value and the B-mode ultrasonic echo data.

8. The apparatus of claim 7, wherein determining the brightness of the combined ultrasound image according to the magnitude relationship between the brightness of the image in the blood flow imaging mode and a brightness threshold and the B-mode ultrasound echo data comprises:

obtaining brightness X of B mode ultrasonic image_BBrightness X of image in blood flow imaging mode_S-Flow；

At X_S-Flow≤threshold_S-F1owWhen X is equal to X_B(ii) a X is the brightness of the combined ultrasonic image;

at X_S-Flow＞threshold_S-FlowWhen X is equal to X_S-Flow+αX_B256; alpha is a coefficient;

among them, threshold_S-FIs the minimum brightness level threshold for the flow imaging mode.

9. The apparatus of claim 8, wherein α is one of:

α＝(256-(X_S-Flow-threshold_S-Flow))；

α＝255/(X_S-Flow-threshold_S-Flow)。

10. the apparatus of any of claims 1 to 9, wherein the method further comprises:

when the n echo signals and the B-mode ultrasonic echo data are obtained, alternately obtaining a B-mode receiving line and a receiving line of a blood flow imaging mode until a complete B-mode image and a complete image of the blood flow imaging mode are obtained;

alternatively, the first and second electrodes may be,

and when the n echo signals and the B-mode ultrasonic echo data are acquired, alternately acquiring a frame of B-mode image and a multi-frame blood flow imaging mode image.

11. An ultrasound apparatus, characterized in that it comprises an ultrasound blood flow imaging device according to any of claims 1 to 10.

Technical Field

The invention relates to the technical field of image processing, in particular to an ultrasonic blood flow imaging device and ultrasonic equipment.

Background

In the ultrasound two-dimensional grayscale image, tissues or organs are imaged at different grayscale levels according to the scattering intensity of the reflector or the imaging point. In a two-dimensional grayscale image, blood inside the vessel appears black (no echo), while the vessel wall appears as a bright border.

To enhance the blood cells in the grayscale image, the level of the transmitted pulse can be increased, thereby making the red blood cell echo stronger. However, when the echo of the red blood cells is enhanced, the echo of the surrounding tissue is also enhanced, that is, the thermal noise and the tissue signal are also increased, and artifacts may appear in the blood flow image. Such as the appearance of color in the vessel wall.

Color flow patterns are the most common patterns used in two-dimensional ultrasound images to show blood flow. In color flow mode, two different sets of transmit signals are transmitted to simultaneously display the blood flow and surrounding tissue. One set of transmit signals is used for grayscale images and the other set is used for flow images. After the ultrasonic probe receives the echo signals from the two transmitted signals, the ultrasonic system processes the echo signals to form a gray scale image and a blood flow image. The blood flow image is then superimposed on the grayscale image, and a single display image is generated by the system.

However, in the color blood flow mode, due to the use of long emission pulses and the method of displaying the grayscale image and the blood flow image in a superimposed manner, different color artifacts occur on the blood vessel wall, color covering tissues and bright reflectors, and how to remove the artifacts is a problem that needs to be solved urgently by those skilled in the art when improving the color blood flow image.

Disclosure of Invention

In view of this, embodiments of the present invention provide an ultrasonic blood flow imaging apparatus and an ultrasonic device, so as to solve the problem that an artifact occurs in an ultrasonic blood flow image in the existing scheme.

According to a first aspect, embodiments of the present invention provide an ultrasonic blood flow imaging apparatus, the apparatus comprising: a memory having at least one program instruction stored therein, and a processor that, upon loading and executing the at least one program instruction, performs the steps of:

transmitting ultrasonic pulses in an interleaving transmitting and receiving mode in a blood flow imaging mode, and receiving n echo signals, wherein n is an integer greater than 1;

acquiring differential signals d (t) of n echo signals;

carrying out amplitude detection on the n echo signals to obtain an envelope curve of each echo signal, and obtaining the sum B (t) of the envelope curves of the echo signals;

calculating image gray scale intensity of a blood flow imaging mode according to the d (t) and the B (t);

acquiring B-mode ultrasonic echo data;

and scanning and converting the B-mode ultrasonic echo data and the calculated image gray intensity of the blood flow imaging mode, and displaying an ultrasonic image according to a conversion result.

Optionally, the transmitting the ultrasonic pulse in the blood flow imaging mode by interleaving transmission and reception includes:

starting the transmitting and receiving of the jth group of receiving lines, wherein the starting value of j is 1;

and after the jth group of receiving lines is received, j +1 is carried out, and the step of starting the transmitting and receiving of the jth group of receiving lines is immediately executed.

Optionally, the calculating an image gray scale intensity of the blood flow imaging mode according to the d (t) and the b (t) includes:

according to the B (t) and a preset threshold value N_tholdUpdating the value of B (t);

and calculating the image gray intensity of the blood flow imaging mode according to the d (t) and the updated B (t).

Optionally, the above is based on the above B (t) and a preset threshold N_tholdUpdating the value of b (t), including:

if B (t)<N_tholdThen N will be_tholdAs updated b (t).

Optionally, the calculating the image gray scale intensity of the blood flow imaging mode according to d (t) and the updated b (t), includes:

the image gray scale intensity of the blood flow imaging mode is as follows:the method can further comprise the following steps:

optionally, the performing scan conversion on the B-mode ultrasonic echo data and the calculated image gray-scale intensity of the blood flow imaging mode, and displaying the ultrasonic image according to the conversion result includes:

and combining the B-mode ultrasonic echo data and the image in the blood flow imaging mode, and displaying the combined ultrasonic image.

Optionally, the combining the B-mode ultrasound echo data and the image of the blood flow imaging mode, and displaying the combined ultrasound image includes:

and determining the brightness of the combined ultrasonic image according to the magnitude relation between the brightness of the image in the blood flow imaging mode and a brightness threshold value and the B-mode ultrasonic echo data.

Optionally, the determining the brightness of the combined ultrasound image according to the size relationship between the brightness of the image in the blood flow imaging mode and the brightness threshold and the B-mode ultrasound echo data includes:

obtaining brightness X of B mode ultrasonic image_BBrightness X of image in blood flow imaging mode_S-Flow；

At X_S-Flow≤threshold_S-FlowWhen X is equal to X_B(ii) a X is the brightness of the combined ultrasonic image;

at X_s-Flow＞threshold_S-FlowWhen X is equal to X_S-Flow+αX_B256; alpha is a coefficient;

among them, threshold_S-FlowIs the minimum brightness level threshold for the flow imaging mode.

Optionally, α is one of:

α＝(256-(X_s-Flow-threshold_S-Flow))；

α＝255/(X_S-Flow-threshold_S-Flow)。

optionally, the performing scan conversion on the B-mode ultrasonic echo data and the calculated image gray-scale intensity of the blood flow imaging mode, and displaying the ultrasonic image according to the conversion result includes:

displaying a B mode ultrasonic image according to the B mode ultrasonic echo data;

and displaying the blood flow image according to the image gray intensity of the blood flow imaging mode.

Optionally, the method further includes:

and when the n echo signals and the B-mode ultrasonic echo data are acquired, alternately acquiring a B-mode receiving line and a receiving line of a blood flow imaging mode until a complete B-mode image and a complete image of the blood flow imaging mode are acquired.

Optionally, the method further includes:

and when the n echo signals and the B-mode ultrasonic echo data are acquired, alternately acquiring a frame of B-mode image and a multi-frame blood flow imaging mode image.

In a second aspect, an ultrasound apparatus is provided, which comprises the ultrasound blood flow imaging device of the first aspect.

After differential signals d (t) of n echo signals and the sum B (t) of the envelope curve of each echo signal are obtained through calculation, the image gray level intensity of a blood flow imaging mode is calculated according to d (t) and B (t), and then an ultrasonic image is displayed according to B-mode ultrasonic echo data and the calculated image gray level intensity when ultrasonic imaging is carried out; the problem of artifacts in ultrasonic images in the prior art is solved; the problem of artifacts in the image due to tissue motion flickering and weak blood flow is solved.

Drawings

In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, 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 without creative efforts.

Fig. 1 is a block diagram of an ultrasound apparatus according to an embodiment of the present invention.

Fig. 2 is a flowchart of a method of ultrasonic blood flow imaging according to an embodiment of the present invention.

Fig. 3 is a schematic diagram of the time of interleaving the transmitted ultrasonic pulses according to the embodiment of the present invention.

Fig. 4 is a schematic diagram of an ultrasound blood flow image obtained using a prior art method.

Fig. 5 is a schematic diagram of an ultrasound blood flow image obtained by the method of the present embodiment according to the present invention.

Detailed Description

The invention is further illustrated by the following specific figures and examples.

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 clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are some, but not all, embodiments of the present invention. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.

For ease of understanding, the related art of the present application will be briefly described. The scheme of the application is applied to an ultrasonic device, and as shown in fig. 1, the ultrasonic device comprises:

a waveform generator: for generating a data signal such that the pulse generator generates a transmit pulse in dependence on the data signal.

Transmit beam combiner: the electronic focusing and the control of the acoustic beam of the multi-array element ultrasonic probe are realized. And delays the transmitted signal appropriately for each array element so that the transmitter signals arrive at the target at the same time and produce the highest acoustic intensity at the target, i.e. the strongest echo signal is acquired.

A pulse generator: for generating the transmit pulse.

T/R switch: and the transmitting and receiving switch is used for controlling the ultrasonic probe to be in a transmitting mode or a receiving mode currently.

An ultrasonic probe: the piezoelectric element is composed of a piezoelectric element, a connector and a supporting structure. The ultrasound probe converts electrical energy into mechanical energy in a transmit mode, and the resulting mechanical waves propagate toward a medium. In the receive mode, the reflected mechanical waveform is received and converted to an electrical signal by the ultrasound probe.

TGC gain: the gain of the amplifier is controlled to increase with the increase of the detection depth so as to compensate the attenuation of the ultrasonic signal with the propagation distance.

An analog-to-digital converter: for converting an analog signal to a digital signal.

A receiving beam synthesizer: similar to the transmitting beam synthesizer, is used for realizing electronic focusing and controlling the sound beam of the multi-array element ultrasonic probe. And the highest sensitivity is achieved by applying appropriate delays to the received echoes to achieve linear superposition of the echo signals from the multiple array elements.

Matching a filter: a filter matched to the transmit code effects compression of the code.

Transverse filter: for performing range sidelobe suppression on the received signal.

A first processing unit: for implementing addition, subtraction or bypass functions. Wherein, bypassing means that the information flow directly enters the next functional module.

Memory: for buffering data, for example, buffering the received echo signal or the processed echo signal. In practical implementation, the memory may be a volatile memory (such as a random-access memory (RAM); the memory may also include a non-volatile memory (such as a flash memory), a hard disk (HDD) or a solid-state drive (SSD); the memory may also comprise a combination of the above kinds of memories.

A band-pass filter: for selecting and filtering a desired frequency band from the received signal.

An amplitude detector: for detecting the amplitude of the received signal.

A second processing unit: for performing addition and bypass functions.

A logarithmic compressor: for performing a logarithmic operation on the received signal.

A third processing unit: for performing a subtraction or bypass function.

Scan conversion/display: for performing data transformation to make the display of the ultrasound image.

Referring to fig. 1, in B mode, the waveform generator generates the desired wideband pulse, which is appropriately delayed by the transmit beam combiner before entering the pulse generator. The pulse generator will then generate and send a high voltage pulse to the ultrasound probe. In the B-mode reception, echo signals of the ultrasonic probe are first amplified by TGC (Time Gain compensation), then converted into digital signals by an analog-to-digital converter, and then delayed and added by a reception beam combiner. The beamforming may be one receive line or multiple receive lines. For the fundamental wave B-mode image, the beamformed data directly enters the bandpass filter, that is, the first processing unit in the image realizes the bypass function (the bypass function described in this embodiment means that the first processing unit skips the unit and enters the next unit for further processing), and the beamformed data directly enters the bandpass filter. For tissue harmonic images, two transmitted pulses with opposite phases exist, the beam synthesis data from the first pulse is stored in a memory, when the beam synthesis data from the second pulse appears, the system adds the two times of beam synthesis data, namely the first processing unit in fig. 1 realizes an adding function, so that fundamental wave signals of the two beam synthesis data are eliminated, second harmonic signals are added, the sum of the second harmonic signals enters a band-pass filter, and the signals processed by the band-pass filter are processed by scanning conversion.

For a blood flow imaging mode, the waveform generator will generate coded pulses according to a predetermined code sequence, typically a binary phase code, such as a Barker (Barker) code or a Golay pair code. The coded pulses are appropriately delayed by the transmit beam combiner before entering the pulse generator. The pulse generator will then generate and send high voltage coded pulses to the ultrasound probe. The echo signals received from the ultrasound probe will first be amplified by the TGC and then converted to digital signals by an analog/digital converter. Since the transmitted pulse is encoded, the echo signal received by the probe contains encoded information, i.e. an encoded echo signal. These digitized coded echo signals will be delayed and summed by the receive beamformer.

When the coding sequence is a barker code, the pulse compression (or decoding) process of the beam-formed data is performed by a matched filter and a transversal filter. The RSL (Range Sidelobe) level of the matched filter barker code is a few decibels lower than that of the main peak, and therefore, a transversal filter is provided to reduce the RSL to 30 decibels or lower, that is, the transversal filter achieves Range Sidelobe suppression. The decoded signal may be stored in a memory or may be added, subtracted or bypassed by the first processing unit. When the transmit code sequence is selected as a Golay pair of codes, the pulse compression process for the beamformed data would be a matched filter matching and summing process, with a single Golay pair of codes being transmitted. The first Golay-encoded beamformed data will be match filtered and stored in memory. The second Golay-encoded beamformed data will be matched, filtered and summed with the first data in memory. The transversal filter will be bypassed because the summation process will cancel the RSL. Using barker codes has the advantage of a single transmission, but requires an additional filter to suppress the RSL. Using Golay pair codes would completely cancel RSL but would require two transmissions slowing down the frame rate.

After the addition, the subtraction or the bypass of the first processing unit, the echo signals in the B mode and the blood flow imaging mode are subjected to band pass filtering, the band pass filter keeps the echo signals in a required frequency band and suppresses noise outside the frequency band, which is beneficial to improving the signal to noise ratio, then the amplitude of the echo signals is calculated by removing the carrier frequency, and the detected amplitude can be stored in a memory or can be summed by the second processing unit. And then, the processed data passes through the second processing unit and the output is stored in the memory, and naturally, the subtraction/bypass processing can also be performed through the third processing unit. After the B-mode ultrasonic echo data and the blood flow imaging mode data are obtained through the processing, the B-mode ultrasonic echo data and the blood flow imaging mode data can be scanned and converted and transmitted to a display for displaying.

In various embodiments herein, the first processing unit, the second processing unit, and the third processing unit may respectively correspond to a processor, or at least two processing units may correspond to one processor, which is not limited in this embodiment.

Referring to fig. 2, a flowchart of a method of an ultrasonic blood flow imaging method provided by an embodiment of the present application is shown, and is used in the ultrasonic apparatus shown in fig. 1, as shown in fig. 2, the method includes:

step 101, transmitting ultrasonic pulses in an interleaving transmitting and receiving mode in a blood flow imaging mode, and receiving and storing n echo signals;

the ultrasound apparatus sets the pulse repetition time PRT between two consecutive transmissions to τ depending on the blood flow velocity. Minimum PRT (τ)_min) Equal to the time required for one transmission and reception. In general, to detect slow blood flow movements, such as blood entering arterioles and capillaries from major vessels, or, in detecting venous blood flow, τ needs to be increased so that the change in phase of the doppler shift signal from one pulse to the next can be measured. Yet simpleIncreasing τ results in a slower frame rate of the ultrasound image, and therefore, in conjunction with fig. 3, the present embodiment transmits the pulse signal by interleaving transmission.

The ultrasound probe initiates a first transmission and reception of a first set of receive lines. The number of receiving lines i, i in each group is more than or equal to 1, and the waiting time tau_minThereafter, reception of the first group of reception lines is completed. The ultrasound probe will initiate the transmit and receive processes for the second set of receive lines without waiting for a time τ. The ultrasound probe will repeat this operation until the first transmission and reception of the mth set of receive lines is completed. Thereafter, the ultrasound probe will initiate a second transmission and reception of the first set of receive lines, which will continue until the second transmission and reception of the mth set is complete. This process will continue until the nth transmit and receive of the mth set of receive line groups. Then the ultrasonic probe moves to the (m +1) th group to receive the wire, and the interweaving process is repeated by adopting the similar transmitting and receiving mode.

The echo signal is e (t) ═ A (t) cos (w)₀t). Wherein, w₀Is the angular frequency of the pulse, and a (t) is the envelope signal. When n ultrasonic pulses are continuously transmitted, the echo signals of the n ultrasonic pulses are respectively e₁(t)、e₂(t)、…、e_n(t)。

In practical implementation, since there may be a loss after the ultrasonic pulse is transmitted and the echo signal cannot be received, the number of the ultrasonic pulses transmitted in this embodiment may be greater than the number of the received echo signals, which is not limited herein.

Step 102, obtaining differential signals d (t) of n echo signals;

when the number of n is 2, the ratio,

when the number of n is 3, the ratio,

where c is the speed of sound, τ is the pulse repetition time, and v is the moving speed of the moving target along the beam direction, where a (t) is the envelope signal used to display the reflection or scattering intensity of the target tissue.

When n is 2, two beamformed echo signals e can be received after the transmission of two coding pulses₁(t) and e₂(t) of (d). Wherein, after TGC gain and analog-to-digital conversion, and referring to the above description, when coded transmission using barker codes, the echo signal will be filtered by the matched filter and range sidelobe suppressed by the transversal filter, and when coded transmission using Golay, the echo signal will be filtered only by the matched filter and directly bypass the transversal filter, at e₁And (t) after the above processing, storing the data in the memory. Thereafter, e₁(t) obtaining | e by amplitude detection after filtering with a band-pass filter₁(t) |, and stored in memory. When e is₂(t) after the above-mentioned treatment, the first processing unit calls e from the memory₁(t) to perform subtraction e₁(t)-e₂(t), namely d (t), and after d (t) is obtained through calculation, d (t) is stored in the memory.

When n is 3, the ultrasonic probe transmits three coded pulses and receives three beamformed echoes e₁(t),e₂(t) and e₃(t) of (d). When e is₁(t) after processing, storing in memory, and simultaneously performing amplitude detection after filtering with a band-pass filter to obtain | e₁(t) |, stored in memory. When e is₂(t) after processing, and with reference to FIG. 1, the first processing unit calls e from memory₁(t) to realize e₁(t)-2e₂(t) and storing it in memory, at the same time as at e₂(t) amplitude detection after band-pass filter filtering to obtain | e₂(t) |. When e is₃(t) after processing and band-pass filter and amplitude detection, the first processing unit passes e₃(t) and e in memory₁(t)-2e₂(t) adding to realize e₁(t)-2e₂(t)+e₃(t) second order filtering to obtain d (t).

103, carrying out amplitude detection on the n echo signals to obtain an envelope curve of each echo signal, and obtaining the sum B (t) of the envelope curves of the echo signals;

when n is equal to 2, the compound is,

when n ═ 3, b (t) ≈ 3a (t);

in practice, when n is 2, e₁And (t) after being processed, the data is stored in the memory. In obtaining e₂After (t), e₂(t) is filtered by a band-pass filter and amplitude-detected to become | e₂(t) |. In conjunction with FIG. 2, the second processing unit processes | e₂(t) | and | e stored in memory₁(t) | is added to obtain | e₁(t)|+|e₂(t) |, and thereby B (t).

Similarly, when n is 3, when e₁(t) after processing, storing in the memory, and simultaneously performing amplitude detection to obtain | e₁(t) |, stored in memory. When e is₂(t) after treatment, e₂(t) filtering with a band-pass filter and performing amplitude detection to obtain | e₂(t) |, and stored in memory. In obtaining e₃After (t), e₃(t) is filtered by a band-pass filter and amplitude-detected to become | e₃(t) |, then the second processing unit stores | e |, in the memory₂(t) | and | e₁(t) | is added to obtain | e₁(t)|+|e₂(t)|，|e₁(t)|+|e₂(t) | will be stored in memory again. The second processing unit will | e₃(t) | and | e in memory₁(t)|+|e₂(t) | is added to obtain | e₁(t)|+|e₂(t)|+|e₃(t)|。

Step 104, calculating the image gray scale intensity of the blood flow imaging mode according to d (t) and B (t);

the method comprises the following steps: gray scale intensity of images in blood flow imaging modeIn order to realize the purpose,

as can be seen from the above description, the gray scale intensity of the echo signal in the blood flow imaging mode is independent of a (t), so that the tissue motion flicker and weak blood flow caused by a (t) can be eliminated by the above-mentioned acquisition mode.

Optionally, in the calculationWhile, can also be rightAnd carrying out logarithmic compression, and representing the gray intensity of the image according to the numerical value after the logarithmic compression.That is, when n is 2, the third processing unit obtains the image gray scale intensity log (| e) of the blood flow pattern₁(t)-e₂(t)|)-log(|e₁(t)|+|e₂(t) |). When n is 3, the third processing unit obtains the image gray scale intensity log (| e) of the blood flow mode₁(t)-2e₂(t)+e₃(t)|)-log(|e₁(t)|+|e₂(t)|+|e₃(t)|)。

In the above description, only by way of example, the image gray scale intensity of the blood flow imaging mode is calculated in the above manner, and in practical implementation, the step includes:

firstly, according to B (t) and a preset threshold N_tholdUpdating the value of B (t);

when n is 2, | e₁(t)|+|e₂(t) | corresponds to a preset threshold value N_tholdIn B (t)<N_tholdWhen B (t) is replaced by N_thold(ii) a Similarly, if B (t) when n is 3<N_tholdReplacing B (t) with N_thold. By setting the above-mentioned preset threshold, noise in B-mode ultrasound can be suppressed, preventing noise from being amplified and displayed in the blood flow mode image.

Secondly, calculating the image gray scale intensity of the blood flow imaging mode according to the d (t) and the updated B (t).

After updating b (t), the gray level intensity of the S-Slow image can be calculated according to d (t) and updated b (t), and the specific calculation method is as described above, and is not described herein again.

In addition, only n is 2 or 3, and in actual implementation, when n is a larger value, the calculation may be performed in a similar manner as described above, and details are not repeated here.

105, acquiring B-mode ultrasonic echo data;

the ultrasonic equipment can also transmit pulses through the ultrasonic probe so as to obtain B-mode ultrasonic echo data. Due to the different requirements of the emission pulses of the B mode and the blood flow imaging mode, the B mode and the blood flow imaging mode data can be acquired and processed differently, that is, the B mode ultrasonic echo data and the echo of the blood flow imaging mode can be obtained through different sequence pulses. For example, B-mode receive lines and blood flow imaging mode receive lines may be obtained alternately until a complete B-mode image and blood flow imaging mode image are obtained; of course, in practical implementation, it is also possible to alternately obtain one frame of B-mode image and one frame of blood flow imaging mode image, and to obtain a higher frame rate of the blood flow imaging mode, it is possible to alternately obtain one frame of B-mode image and multiple frames of blood flow imaging mode image.

In practical implementation, when obtaining B-mode ultrasonic echo data, harmonic data may be obtained, or fundamental data may be obtained, which is not limited in this embodiment.

And 106, performing scanning transformation on the B-mode ultrasonic echo data and the calculated image gray intensity of the blood flow imaging mode, and displaying the ultrasonic image according to the transformation result.

In practical implementation, the images in the B-mode ultrasound and blood flow imaging modes may be displayed separately, or may be displayed side by side, or of course, may be displayed in combination. In this embodiment, after acquiring the B-mode ultrasound echo data and the image data in the blood flow imaging mode, the two data are combined together and displayed, for example, the step includes: and combining the B-mode ultrasonic echo data and the image in the blood flow imaging mode, and displaying the combined ultrasonic image. In practical implementation, the method for combining the two images includes: and determining the brightness of the combined ultrasonic image according to the magnitude relation between the brightness of the image in the blood flow imaging mode and a brightness threshold value and the B-mode ultrasonic echo data.

Specifically, the method comprises the following steps:

first, the brightness X of the B-mode ultrasound image is obtained_BBrightness X of image in blood flow imaging mode_S-Flow；

Second, in X_S-Flow≤threshold_S-FlowWhen X is equal to X_BAnd X is the brightness of the combined image; among them, threshold_S-FlowMinimum brightness level threshold for blood flow imaging mode, below threshold_S-FlowAre considered to be non-flow imaging mode signals.

Third, in X_S-Flow＞threshold_S-FlowWhen X is equal to X_S-Flow+αX_B/256, where α can be calculated as one of:

(a)α＝(256-(X_S-Flow-threshold_S-Flow))；

(b)

(c)α＝255/(X_S-Flow-threshold_S-Flow)。

referring to fig. 4, it shows an ultrasound blood flow image obtained by using a conventional method, and it can be known from fig. 4 that the obtained ultrasound blood flow image is not smooth enough and has some artifacts; however, referring to fig. 5, it shows the ultrasound blood flow image obtained by the method of this embodiment, which is significantly smoother, and the artifacts are eliminated to a great extent.

In summary, the ultrasound blood flow imaging apparatus provided in this embodiment calculates the difference signal d (t) of n echo signals and the sum B (t) of the envelope curve of each echo signal, and then calculates the image gray scale intensity of the blood flow imaging mode according to d (t) and B (t), so as to display the ultrasound image according to the B-mode ultrasound echo data and the calculated image gray scale intensity during the ultrasound imaging; the problem of artifacts in ultrasonic images in the prior art is solved; the problem of artifacts in the image due to tissue motion flickering and weak blood flow is solved.

Meanwhile, when the gray level intensity of the image is calculated in the embodiment, the gray level intensity of the image is calculated by calculating the difference value of the logarithmic values of the image and the logarithmic values of the image, so that the effects of eliminating artifacts, realizing by simple subtraction and having low processing complexity are achieved.

The present embodiments also provide an ultrasound apparatus, the apparatus comprising: the ultrasonic blood flow imaging system comprises a memory and a processor, wherein at least one program instruction is stored in the memory, and the processor is used for realizing the ultrasonic blood flow imaging method by loading and executing the at least one program instruction.

The embodiment also discloses an ultrasonic device which comprises the ultrasonic blood flow imaging device.

An embodiment of the present invention further provides a non-transitory computer storage medium, where the computer storage medium stores computer-executable instructions, and the computer-executable instructions may execute the ultrasound blood flow imaging method in any of the above method embodiments. The storage medium may be a magnetic Disk, an optical Disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a Flash Memory (Flash Memory), a Hard Disk (Hard Disk Drive, abbreviated as HDD), a Solid State Drive (SSD), or the like; the storage medium may also comprise a combination of memories of the above kind.

Although the embodiments of the present invention have been described in conjunction with the accompanying drawings, those skilled in the art may make various modifications and variations without departing from the spirit and scope of the invention, and such modifications and variations fall within the scope defined by the appended claims.