CN103300888A - High-frequency ultrasonic superficial organ imaging method capable of lowering random noise - Google Patents
High-frequency ultrasonic superficial organ imaging method capable of lowering random noise Download PDFInfo
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- CN103300888A CN103300888A CN2013101646651A CN201310164665A CN103300888A CN 103300888 A CN103300888 A CN 103300888A CN 2013101646651 A CN2013101646651 A CN 2013101646651A CN 201310164665 A CN201310164665 A CN 201310164665A CN 103300888 A CN103300888 A CN 103300888A
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Abstract
The invention discloses a high-frequency ultrasonic superficial organ imaging method capable of lowering random noise. The method is characterized in that an ultrasonic transducer continuously transmits N times of ultrasonic pulses at intervals within a dwell time of 200 microseconds on each scanning position in a scanning area, after the superimposition average operation processing is carried out by adopting a linear average method for the ultrasonic echo information, and the processing result is used as a scanning line of the scanning position; and then the scanning position is moved to repeat the process until all scanning lines are completed, and the two-dimensional high-frequency ultrasonic imaging can be realized. The echo information acquired through N times of detection is superimposed and averaged by adopting the linear average method, the random noise in the echo information of the scanning line is lowered, the signal-to-noise can be theoretically improved by N times, no frame frequency is reduced, and the imaging real-time property is not influenced. Since the N-time sampling time anticipating in the average calculation is about 200 microseconds, a probe and a tissue can be easily maintained relatively still, and the ghosting phenomenon caused by the frame average technology can be avoided.
Description
Technical field
The present invention relates to a kind of method for ultrasonic imaging, relate in particular to a kind of high frequency ultrasound superficial organ's formation method that can reduce random noise.
Background technology
The principle of ultra sonic imaging is to launch ultrasonic pulse by ultrasonic transducer to tissue, then receive the echo that is reflected by tissue, thereby obtain the one-dimension information of the tissue on the transonic passage, translation or rotate ultrasonic transmit direction, constantly launch simultaneously ultrasonic and reception of echoes, will obtain the organizational information (see figure 1) of the scanned plane domain of acoustic beam, these information are rebuild, can obtain the two-dimentional tangent plane picture of tissue, i.e. usually said B ultrasonic image.
Echo information is very faint, therefore need to amplify a lot of times and just can have random noise in this process and be exaggerated with echo signal for observing, these random noises become background noise in image, it can affect the performance of real information, even floods some relatively faint echo information.
The superposed average method of image is the effective ways of Removing Random No commonly used in the ultrasonic imaging technique.Its principle is based on random noise non-correlation in time, namely same position is carried out Multiple-Scan, and the echo information of organizing that each scanning tissue obtains is identical, and the random noise in the echo is all different.Therefore, will carry out superposed average to several ultrasonograms that same scanning area multiple scanning obtains, and can make random noise cancel out each other and do not reduce and organize echo information.To offset fully through random noise after infinite the stack in theory.Impossible unconfined stack in the practical application, otherwise can't carry out realtime imaging.General method is to adopt the average method of frame, in the situation that requirement of real-time not bery high (as to static organ imaging the time) adopts limited number of time stack (be no more than 8 times), can effectively reduce random noise.The precondition that adopts this method is that the useful information of a series of images is constant, that is: 1) organ that is scanned changes without form during Multiple-Scan; 2) probe positions constant (namely scanning is same position) during the Multiple-Scan.Otherwise image will produce ghost image, thicken unclear.Generally to the speed (frame frequency) of static organ ultra sonic imaging about per second 10 frames, be that interval time is about 100ms between every frame, probe is unavoidable therebetween, and small movement occurs, if adopt multi-frame mean, then the time also can be multiplied, and the probability that probe or histoorgan move is larger.During the ultra sonic imaging of common frequencies, resolving power is in the millimeter magnitude, and therefore when the static organ of scanning, the micro-displacement that can not cause because of vibration and operator's hand hold transducer shakiness of probe causes ghost image.And when high frequency ultrasound imaging, when especially supersonic frequency was higher than 35MHz, the resolving power of image can reach tens microns, thereby the displacement of small vibration or probe all can cause the relatively large variation of image.And the operator is difficult to probe stationary in this precision, the therefore unavoidable ghost image that produces, and this shortcoming causes the application of this technology in high frequency ultrasound imaging to be restricted.
The investigation depth of supersonic imaging apparatus is directly proportional with the time of reception of reception of echoes information.The maximum probe degree of depth of common supersonic imaging apparatus is about 18cm, and the echo time of reception of corresponding every scanning line is more than the 200 μ s, thus general transducer at a position time of staying T in the above (see figure 2) of 250 μ s.And the investigation depth of the supersonic imaging apparatus more than the 35MHz is about 1/10th of common supersonic imaging apparatus, the echo time of reception also is about the former 1/10th, namely approximately in the 30 μ s, all the other approximately 80% time be idle waiting state (see figure 3), this has just created essential condition for the realization of line averaging.
Summary of the invention
For above-mentioned situation, the invention provides high frequency ultrasound superficial organ's formation method that can reduce random noise.The present invention reaches the noise reduction same with the frame averaging under the prerequisite that does not reduce frame frequency, and can therefore not produce ghost image.
For achieving the above object, a kind of high frequency ultrasound superficial organ's formation method that can reduce random noise of the present invention, it is each scanning position in scanning area, ultrasonic transducer is equally spaced launched the repeated ultrasonic pulse continuously in time of staying T is 150 μ s～250 μ s, after adopting the line averaging method that ultrasonic echo information is carried out the superposed average calculation process, as the scanning line of this scanning position; Realize two-dimentional high frequency ultrasound imaging after finishing the scanning line of all scanning positions in the whole scanning area.
Further, the present invention can reduce high frequency ultrasound superficial organ's formation method of random noise, wherein, the repeated ultrasonic pulse process of described ultrasonic transducer emission is by echo receive path, buffering selector, variable connector, N the circuit that buffer, adder, linear memory and address pointer form; And may further comprise the steps:
Be set with m scanning position in scanning area, the initial position 1 of ultrasonic transducer self-scanning moves to last scanning position m successively; Ultrasonic transducer is equally spaced launched N ultrasonic pulse continuously in the time of staying of each scanning position T, and by echo receive path reception ultrasonic echo information, the time T r of ultrasonic pulse number N, the ultrasonic reception of echo, the relation between the time of staying T are: N * Tr＜T, wherein, N=2～8; By buffering selector control variable connector that the N group ultrasonic echo information that receives is temporary to buffer 1～buffer N successively; N in N buffer group ultrasonic echo information is read simultaneously, according to the following equation N is organized ultrasonic echo information by adder and carry out superposed average computing, A
i=(A
I1+ A
I2+ ...+A
IN)/N, wherein, i is current scanning position, the value of i is followed successively by 1,2, and 3 ... m, thus form as preceding article scanning line A
iUltrasonic echo information; With the address of the current scanning position i of address pointer Direction Line memorizer, with after the stack as preceding article scanning line A
iUltrasonic echo information deposit to this address location, thereby, finished processing and storage when the preceding article scanning line; By that analogy, finish the scanning line A of m scanning position
1～A
m, obtain the information of whole scanning area, form two-dimensional ultrasonic image.
Compared with prior art, the invention has the beneficial effects as follows:
According to the difference of investigation depth, transducer a certain position retention period continuous, take greater than the echo time of reception as N ultrasonic pulse A of equally spaced emission
11～A
1NSuch as Fig. 4, the echo information that the present invention adopts the line averaging method that N detection obtained is carried out superposed average, to the random noise in the echo information of this scanning line be reduced, can improve in theory signal to noise ratio N doubly, the average effect of its noise reduction and N frame is identical, but does not reduce frame frequency, does not affect the real-time of imaging.In addition, only finish at time T=150 μ s～250 μ s owing to participating in N sampling of average computation, within the so short time, be easy to maintenance pop one's head in and organize relatively static, thereby can not produce the ghost phenomena that the frame averaging causes.
Description of drawings
Fig. 1 is two-dimensional ultrasonic imaging process schematic diagram;
Fig. 2 is common ultrasonic scanning line sampling time schematic diagram;
Fig. 3 is high frequency superficial organ ultrasonic scanning line sampling time schematic diagram of the present invention;
Fig. 4 is the Centre Line Average scanning line of the present invention schematic diagram of repeatedly launching, sample;
Fig. 5 realizes the schematic block circuit diagram that the line averaging method is processed among the present invention;
Fig. 6 realizes the schematic block circuit diagram that the line averaging method is processed in the embodiment of the invention;
Fig. 7 is the original image of not processing through the line averaging method;
Fig. 8 gets m=500 in the embodiment of the invention, T=200 μ s, Tr=23 μ s, the image during N=4.
Specific implementation method
Below in conjunction with specific implementation method the present invention is described in further detail.
The present invention can reduce high frequency ultrasound superficial organ's formation method of random noise, it is each scanning position in scanning area, ultrasonic transducer is equally spaced launched the repeated ultrasonic pulse continuously in time of staying T is 150 μ s～250 μ s, adopt the line averaging method that ultrasonic echo information is carried out the superposed average calculation process during sampling, to reducing random noise, process rear scanning line as this scanning position; Realize two-dimentional high frequency ultrasound imaging after finishing the scanning line of all scanning positions in the whole scanning area.As shown in Figure 5, the repeated ultrasonic pulse process of described ultrasonic transducer emission is by echo receive path, buffering selector, variable connector, N the circuit that buffer, adder, linear memory and address pointer form.
The present invention can reduce high frequency ultrasound superficial organ's formation method of random noise, may further comprise the steps: be set with m scanning position in scanning area, the initial position 1 of ultrasonic transducer self-scanning moves to last scanning position m successively; Ultrasonic transducer is equally spaced launched N ultrasonic pulse continuously in the time of staying of each scanning position T, and by echo receive path reception ultrasonic echo information, the time T r of ultrasonic pulse number N, the ultrasonic reception of echo, the relation between the time of staying T are: N * Tr＜T, wherein, N=2～8, as shown in Figure 3; By buffering selector control variable connector that the N group ultrasonic echo information that receives is temporary to buffer 1～buffer N successively; N in N buffer group ultrasonic echo information is read simultaneously, according to the following equation N is organized ultrasonic echo information by adder and carry out superposed average computing, A
i=(A
I1+ A
I2+ ...+A
IN)/N, wherein, i is current scanning position, the value of i is followed successively by 1,2, and 3 ... m, thus form as preceding article scanning line A
iUltrasonic echo information; With the address of the current scanning position i of address pointer Direction Line memorizer, with after the stack as preceding article scanning line A
iUltrasonic echo information deposit to this address location, thereby, finished processing and storage when the preceding article scanning line; By that analogy, finish the scanning line A of m scanning position
1～A
m, obtain the information of whole scanning area, form two-dimensional ultrasonic image.
Embodiment:
Scanning line number m=500, every scanning line time of staying T=200 μ s equally spaced launches the times N of ultrasonic pulse=4 in the time of staying T continuously, echo time of reception Tr=23 μ s, the time that gathers piece image is 100ms.Fig. 6 is the circuit theory diagrams that the embodiment Centre Line Average is processed, and comprises echo information receive path, buffer memory gated counter, 1-4 selector switches, buffer 1～buffer 4, adder, linear memory and address pointer enumerator.Mutual alignment or annexation between them are: the output of echo information receive path has been transformed to 8 echo information of digital signal, its output is connected to the data input pin of buffer 1～buffer 4, buffer memory gated counter control 1-4 selector switches, 4 emission cycles in time T=200 are selected input clock CKin is delivered to buffer 1～buffer 4 successively, buffer 1～buffer 4 is the FIFO(push-up storage of 4 1024 * 8bit), each buffer is receive data within the emission cycle that is strobed only, behind buffer 4 beginning receive datas, export simultaneously the data of buffer 1～buffer 4 to the adder addition by output clock CKout, the output of adder is connected to linear memory, the address of linear memory is produced by line address pointer enumerator, and a scanning position line of every conversion address pointer enumerator adds 1.
When beginning to scan, ultrasonic transducer is in the preliminary sweep position, such as the A among Fig. 1
1The position begins to launch ultrasonic and the reception of echoes signal, such as the A among Fig. 4
11, deposit the signal that the echo receive path comes in buffer 1 by buffer memory gated counter control variable connector.Launch again a branch of ultrasonic and reception of echoes signal, such as the A among Fig. 4
12, the buffer memory gated counter deposits signal in buffer 2 by variable connector, carries out successively this process, until launched 4 times and with the ultrasonic echo information of the 4th, such as the A among Fig. 4
1NDeposit to buffer 4,4 groups of ultrasonic echo information in 4 buffers are read simultaneously, by adder 4 groups of ultrasonic echo information are carried out superposed average computing, that is: A
1=(A
11+ A
12+ A
13+ A
14)/4, thus article one scanning line A formed
1Ultrasonic echo information, as shown in Figure 4; The first scanning position A with address pointer enumerator Direction Line memorizer
1The address, with the stack after article one scanning line A
1Ultrasonic echo information deposit to this address location, thereby, finished processing and the storage of article one scanning line;
Mobile ultrasonic transducer is to the position of second scanning line, such as the A among Fig. 1
2The position begins to launch ultrasonic and the reception of echoes signal, such as the A among Fig. 4
21, deposit the signal that the echo receive path comes in buffer 1 by the buffer memory gated counter by variable connector.Launch again a branch of ultrasonic and reception of echoes signal, such as the A among Fig. 4
22, buffer memory gated counter control variable connector deposits signal in buffer 2, carries out successively this process, until launched 4 times and with the echo information of the 4th, such as the A among Fig. 4
2NDeposit to buffer 4,4 groups of ultrasonic echo information in 4 buffers are read simultaneously, by adder 4 groups of ultrasonic echo information are carried out superposed average computing, that is: A
2=(A
21+ A
22+ ...+A
24)/4, thus second scanning line A formed
2Ultrasonic echo information.As shown in Figure 4; The address pointer enumerator is added 1, the second scanning position A of Direction Line memorizer
2The address, with the stack after second scanning line A
2Ultrasonic echo information deposit to this address location, thereby, finished processing and the storage of second scanning line.
Mobile transducer A to Fig. 1 successively
3, A
4, A
5, until A
500The position, and at 4 ultrasonic and reception of echoes signals of each position emission, deposit in a manner described the relevant position to linear memory after the stack, A among Fig. 5
3, A
4, A
500Overlap-add procedure and the storage of whole scanning area echo information are finished in the position, obtain the information of whole scanning area, form two-dimensional ultrasonic image, as shown in Figure 8.
Fig. 7 is not for adopting the original image of the average overlap-add procedure of line, and its scanning line number m=500, every scanning line time of staying T=200 μ s, echo time of reception are Tr=23 μ s, and the time that gathers piece image is 100ms.Can find out has larger background noise when image is untreated, some small-signals and background noise are difficult for being resolved in same level.
Fig. 8 is the two-dimensional ultrasonic image that forms after embodiment adopts the average addition method of line to process, noise reduction is equivalent to the Overlay of 4 width of cloth images, background noise obviously descends, some faint information are presented out, and the interval of the echo information of each group participation stack is about 200 μ s, probe and the degree that is subjected to displacement of tissue are very little during this time, thereby can not produce ghost image.
Although top invention has been described in conjunction with figure; but the present invention is not limited to the above-mentioned specific embodiment; the above-mentioned specific embodiment only is schematic; rather than restrictive; those of ordinary skill in the art is under enlightenment of the present invention; in the situation that do not break away from aim of the present invention, can also make a lot of distortion, these all belong within the protection of the present invention.
Claims (2)
1. high frequency ultrasound superficial organ's formation method that can reduce random noise, it is characterized in that: each scanning position in scanning area, ultrasonic transducer is equally spaced launched the repeated ultrasonic pulse continuously in time of staying T is 150 μ s～250 μ s, after adopting the line averaging method that ultrasonic echo information is carried out the superposed average calculation process, as the scanning line of this scanning position; Realize two-dimentional high frequency ultrasound imaging after finishing the scanning line of all scanning positions in the whole scanning area.
2. described high frequency ultrasound superficial organ's formation method that can reduce random noise according to claim 1, it is characterized in that, the repeated ultrasonic pulse process of described ultrasonic transducer emission is by echo receive path, buffering selector, variable connector, N the circuit that buffer, adder, linear memory and address pointer form; And may further comprise the steps:
Be set with m scanning position in scanning area, the initial position 1 of ultrasonic transducer self-scanning moves to last scanning position m successively;
Ultrasonic transducer is equally spaced launched N ultrasonic pulse continuously in the time of staying of each scanning position T, and by echo receive path reception ultrasonic echo information, the time T r of ultrasonic pulse number N, the ultrasonic reception of echo, the relation between the time of staying T are: N * Tr＜T, wherein, N=2～8;
By buffering selector control variable connector that the N group ultrasonic echo information that receives is temporary to buffer 1～buffer N successively;
N in N buffer group ultrasonic echo information is read simultaneously, according to the following equation N is organized ultrasonic echo information by adder and carry out superposed average computing, A
i=(A
I1+ A
I2+ ... + A
IN)/N, wherein, i is current scanning position, the value of i is followed successively by 1,2, and 3 ... m, thus form as preceding article scanning line A
iUltrasonic echo information;
With the address of the current scanning position i of address pointer Direction Line memorizer, with after the stack as preceding article scanning line A
iUltrasonic echo information deposit to this address location, thereby, finished processing and storage when the preceding article scanning line;
By that analogy, finish the scanning line A of m scanning position
1～A
m, obtain the information of whole scanning area, form two-dimensional ultrasonic image.
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Cited By (3)
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| CN103876780A (en) * | 2014-03-03 | 2014-06-25 | 天津迈达医学科技股份有限公司 | High-frequency ultrasonic blood flow gray-scale imaging method and high-frequency ultrasonic blood flow gray-scale imaging device |
| CN105342642A (en) * | 2015-11-26 | 2016-02-24 | 无锡海斯凯尔医学技术有限公司 | Elasticity imaging system and elasticity imaging method |
| WO2021120062A1 (en) * | 2019-12-18 | 2021-06-24 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasonic imaging method and ultrasonic imaging system |
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| CN101889873A (en) * | 2009-05-19 | 2010-11-24 | 株式会社东芝 | Diagnostic ultrasound equipment and ultrasound probe |
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Patent Citations (4)
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|---|---|---|---|---|
| US20030216644A1 (en) * | 2002-05-17 | 2003-11-20 | Anne Hall | Display for subtraction imaging techniques |
| US20040059221A1 (en) * | 2002-09-25 | 2004-03-25 | Takashi Azuma | Ultrasonic imaging system and method |
| CN101081171A (en) * | 2006-05-30 | 2007-12-05 | 株式会社东芝 | Ultrasonic diagnostic apparatus, ultrasonic diagnostic method, and control processing program for ultrasonic diagnostic apparatus |
| CN101889873A (en) * | 2009-05-19 | 2010-11-24 | 株式会社东芝 | Diagnostic ultrasound equipment and ultrasound probe |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103876780A (en) * | 2014-03-03 | 2014-06-25 | 天津迈达医学科技股份有限公司 | High-frequency ultrasonic blood flow gray-scale imaging method and high-frequency ultrasonic blood flow gray-scale imaging device |
| CN103876780B (en) * | 2014-03-03 | 2015-07-15 | 天津迈达医学科技股份有限公司 | High-frequency ultrasonic blood flow gray-scale imaging method and high-frequency ultrasonic blood flow gray-scale imaging device |
| CN105342642A (en) * | 2015-11-26 | 2016-02-24 | 无锡海斯凯尔医学技术有限公司 | Elasticity imaging system and elasticity imaging method |
| WO2021120062A1 (en) * | 2019-12-18 | 2021-06-24 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasonic imaging method and ultrasonic imaging system |
| CN114340505A (en) * | 2019-12-18 | 2022-04-12 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasonic imaging method and ultrasonic imaging system |
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