CN106580371B - Doppler ultrasonic blood flow detection device and detection method thereof - Google Patents
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Abstract
The invention discloses a Doppler ultrasonic blood flow detection device which comprises a wall filter 1, an autocorrelation processing module 1, a wall filter 2, an autocorrelation processing module 2, an energy change rate processing module, a blood flow detection module, a scanning conversion processing module and a display module. The detection method of Doppler ultrasonic blood flow detection device comprises the following steps of preliminary judgment; measurement of the energy change rate (Pwr Chg); final judgment; scanning and converting blood flow signals; the resultant display of blood flow and tissue signals. Under the condition that the blood flow is preliminarily judged, the energy change rate (Pwr Chg) needs to be further measured, and the blood flow detection module finally determines whether the blood flow is blood flow or tissue through the energy change rate (Pwr Chg), so that the error rate of blood flow detection can be obviously reduced, and the blood flow detection sensitivity of the ultrasonic equipment cannot be reduced.
Description
Technical Field
The invention particularly relates to a Doppler ultrasonic blood flow detection device and a detection method thereof.
Background
A typical process flow for color doppler ultrasound imaging is shown in fig. 1. After the quadrature demodulated ultrasound blood flow data is acquired, it is fed into a wall filter to attenuate the energy of the low velocity moving tissue signal. After the wall filtering is completed, an autocorrelation process is performed, and at each spatial location of the ultrasound scan, the wall filtered data is used to estimate the average velocity (Vel) and energy (Pwr). After the two ultrasound blood flow related parameters are acquired, the parameters are smoothed spatially and temporally to remove noise, respectively, and then fed into a blood flow detection module to determine whether the location is tissue or blood flow using the blood flow related parameters and B-mode image brightness (Env). The point value is set to 0 if it is tissue, and the blood flow velocity value if it is blood flow. Then, a scan conversion process is performed on the black-and-white signal representing the tissue and the color signal representing the blood flow, and these two signals are converted into signals in rectangular coordinates or polar coordinates. And finally, the display module displays the converted color signals and black-and-white signals in a mode of overlapping in a frame of image, displays the color signals according to the blood flow velocity if the color signals are blood flow, and displays the black-and-white signals according to the brightness of the B mode if the color signals are tissues.
In the process flow of color Doppler ultrasound, blood flow detection is an important module, which affects the blood flow sensitivity and color noise level of the ultrasound device to a great extent. In a typical test, we use the relevant parameters of the blood flow and the B-mode image brightness (Env) to determine whether the current location is tissue or blood flow. The decision logic of the existing blood flow detection module is as follows:
b-mode image brightness (Env) is greater than a defined value, then the point is tissue, otherwise blood flow;
the average velocity (Vel) is less than the defined value, then the point is tissue, otherwise blood flow;
the energy (Pwr) is less than a defined value, then the point is tissue, otherwise blood flow;
if all three of the above determinations are blood flow, then the point is ultimately determined to be blood flow.
Such logical combinations can distinguish between tissue and blood flow in most cases, but when special cases are encountered, it is possible to detect errors.
As shown in fig. 2, the left side is a power spectrum of a case, the high-energy part is tissue, the low-energy part is blood flow, if we set a wall filter with normalized cut-off frequency of 0.2, we can obtain a signal with relatively high energy and normalized average speed of 0.4 after autocorrelation. If both the B-mode luminance (Env) and the energy (Pwr) at this location satisfy the condition of determining blood flow and the threshold of blood flow velocity is 0.25, then the existing blood flow detection module will naturally determine the current point as blood flow.
However, for the signal on the right side of fig. 2, since the cut-off frequency of the wall filter is 0.2, a portion of the tissue signal passes through the wall filter to the autocorrelation measurement module, which also yields a relatively high energy signal with a normalized average velocity of 0.3. Under the same detection threshold condition, the existing blood flow detection module still judges the point as blood flow, but in reality, the point is a tissue motion signal, so that the existing blood flow detection module makes an erroneous judgment.
Disclosure of Invention
The invention aims to overcome the defects of the prior art and provide a Doppler ultrasonic blood flow detection device and a detection method thereof, so as to solve the problem that the existing blood flow detection module erroneously judges a tissue motion signal as blood flow under the special condition.
In order to achieve the above purpose, the technical scheme adopted by the invention is as follows:
in one aspect, a Doppler ultrasound blood flow detection device is provided, comprising
A wall filter 1 for attenuating energy of a tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data);
an autocorrelation processing module 1 for determining average velocity (Vel) and energy (Pwr) using the data processed by the wall filter 1 at each spatial location of the ultrasound scan;
and also comprises
A wall filter 2 having a cutoff frequency different from that of the wall filter 1 for attenuating energy of a tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data);
an autocorrelation processing module 2 for measuring energy (Pwr 2) using the data processed by the wall filter 2;
the energy change rate processing module is used for: using energy (Pwr 2) and energy (Pwr) to measure energy change rate (Pwr Chg) of the wall filter 1 and the wall filter 2 after treatment with different cut-off frequencies;
the blood flow detection module determines whether the position is a tissue or a blood flow by using the average velocity (Vel) and the energy (Pwr) after the smoothing process, and the B-mode image brightness (Env) and the energy change rate (Pwr Chg), measures a blood flow velocity value (Vel 1), and outputs a black-and-white signal indicating the tissue and a color signal indicating the blood flow.
Preferably, also comprises
And the scan conversion processing module is used for performing scan conversion processing on the black-and-white signals representing tissues and the color signals representing blood flow and converting the two signals into rectangular coordinates or a polar coordinate system.
Preferably, also comprises
And the display module is used for overlapping and displaying the signals which are output by the scan conversion processing module and are used for representing the tissues and the blood flow in one frame of image.
Preferably, the device further comprises a smoothing processing module 1, which performs smoothing processing on the average speed (Vel) and the energy (Pwr) output by the autocorrelation processing module 1 in space and time to remove noise;
the smoothing module 2 performs spatial and temporal smoothing on the energy (Pwr 2) output from the autocorrelation processing module 2 to remove noise.
Preferably, the wall filter 1 and the wall filter 2 are both high-pass filters.
Preferably, the wall filter 2 has a cut-off frequency greater than that of the wall filter 1.
In another aspect, a method for detecting a Doppler ultrasound blood flow detection device is provided, comprising the steps of,
s1, preliminary judgment:
attenuating energy of the tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data) by a wall filter 1;
determining, by the autocorrelation processing module 1, at each spatial location of the ultrasound scan, the average velocity (Vel) and the energy (Pwr) using the data processed by the wall filter 1;
the blood flow detection module uses the smoothed average velocity (Vel), energy (Pwr) and B-mode image brightness (Env) to determine whether the location is tissue or blood flow, the determination logic is as follows
B-mode image brightness (Env), greater than a defined value for tissue and less than a defined value for blood flow;
average velocity (Vel), less than a defined value for tissue, greater than a defined value for blood flow;
energy (Pwr), less than a defined value for tissue, greater than a defined value for blood flow;
when all three values of the B-mode brightness (Env), the average speed (Vel) and the energy (Pwr) are judged to be inconsistent, setting a blood flow speed value (Vel 1) at the position to 0, and outputting a black-and-white signal representing the tissue;
and also comprises
S2, measurement of energy change rate (Pwr Chg):
when the blood flow detection module determines that the blood flow is the average velocity (Vel), the energy (Pwr) and the B-mode image brightness (Env) after the smoothing process, the energy change rate (Pwr Chg) is measured;
attenuating energy of a tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data) by a wall filter 2 having a cutoff frequency different from that of the wall filter 1;
the autocorrelation processing module 2 uses the data processed by the wall filter 2 to determine energy (Pwr 2);
the energy change rate processing module adopts energy (Pwr) and energy (Pwr 2) to determine the energy change rate (Pwr Chg) after the wall filter 1 and the wall filter 2 with different cut-off frequencies are processed, and the determination formula is that
S3, final judgment:
the blood flow detection module uses the energy change rate (Pwr Chg) to finally determine whether it is tissue or blood flow, and determines the blood flow velocity value (Vel 1), the determination logic of which is as follows,
the rate of energy change (Pwr Chg), greater than a defined value is tissue, less than a defined value is blood flow;
when it is determined that the tissue is a tissue, the blood flow velocity value (Vel 1) at the position is set to 0, and a black-and-white signal indicating the tissue is output; when it is determined that the blood flow is detected, the blood flow velocity value (Vel 1) at the position is set to the average velocity (Vel) after the smoothing process, and a color signal indicating the blood flow is outputted.
Preferably, the method further comprises the following steps,
s4, blood flow signal scan conversion processing: the scan conversion processing module performs scan conversion processing on a black-and-white signal representing tissue and a color signal representing blood flow, and converts the two signals into signals of rectangular coordinates or a polar coordinate system.
Preferably, the method further comprises the following steps,
s5, synthesizing and displaying blood flow and tissue signals: the display module superimposes the signals representing the tissues and the blood flow output by the scan conversion processing module on one frame of image for display.
Preferably, in the step S1, the smoothing module 1 performs a spatial and temporal smoothing process on the average velocity (Vel) and the energy (Pwr) to remove noise therein;
in the step S2, the smoothing module 2 performs spatial and temporal smoothing on the energy (Pwr 2) to remove noise therein.
The beneficial effects of the invention are as follows:
1. in the invention, when three data of the brightness (Env), the average speed (Vel) and the energy (Pwr) of the B-mode image are all judged to be blood flow, the wall filter 2, the autocorrelation processing module 2, the smoothing processing module 2 and the energy change rate processing module are used for measuring the energy change rate (Pwr Chg), and the blood flow detection module is used for finally determining whether the blood flow is blood flow or tissue according to the energy change rate (Pwr Chg), so that the error rate of blood flow detection can be obviously reduced, and the blood flow detection sensitivity of ultrasonic equipment can not be reduced.
2. The smoothing module 1 performs spatial and temporal smoothing on the average velocity (Vel) and the energy (Pwr) to remove noise therein, and the smoothing module 2 performs spatial and temporal smoothing on the energy (Pwr 2) to remove noise, so that the detection data can be further optimized.
Drawings
FIG. 1 is a flow chart of a prior Doppler ultrasound blood flow detection method;
FIG. 2 is a graph of the ultrasonic power spectrum after the filter 1 is set;
FIG. 3 is a schematic block diagram of a Doppler ultrasound blood flow detection device;
fig. 4 is an ultrasonic power spectrum after the filter 2 is provided.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the technical solutions of the present invention will be clearly and completely described below with reference to specific embodiments of the present invention and corresponding drawings.
Example 1
Referring to fig. 3, the present embodiment provides a doppler ultrasound blood flow detection device, including
A wall filter 1 for attenuating energy of a tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data);
an autocorrelation processing module 1 for determining average velocity (Vel) and energy (Pwr) using the data processed by the wall filter 1 at each spatial location of the ultrasound scan;
and also comprises
A wall filter 2 having a cutoff frequency different from that of the wall filter 1 for attenuating energy of a tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data);
an autocorrelation processing module 2 for measuring energy (Pwr 2) using the data processed by the wall filter 2;
the energy change rate processing module is used for: using energy (Pwr 2) and energy (Pwr) to measure energy change rate (Pwr Chg) of the wall filter 1 and the wall filter 2 after treatment with different cut-off frequencies;
the blood flow detection module determines whether the position is a tissue or a blood flow by using the average velocity (Vel) and the energy (Pwr) after the smoothing process, and the B-mode image brightness (Env) and the energy change rate (Pwr Chg), measures a blood flow velocity value (Vel 1), and outputs a black-and-white signal indicating the tissue and a color signal indicating the blood flow.
And also comprises
And the scan conversion processing module is used for performing scan conversion processing on the black-and-white signals representing tissues and the color signals representing blood flow and converting the two signals into rectangular coordinates or a polar coordinate system.
And also comprises
And the display module is used for overlapping and displaying the signals which are output by the scan conversion processing module and are used for representing the tissues and the blood flow in one frame of image.
The device also comprises a smoothing processing module 1, which performs smoothing processing on the average speed (Vel) and the energy (Pwr) output by the autocorrelation processing module 1 in space and time to remove noise;
the smoothing module 2 performs spatial and temporal smoothing on the energy (Pwr 2) output from the autocorrelation processing module 2 to remove noise.
The wall filter 1 and the wall filter 2 are both high pass filters.
The wall filter 2 has a cut-off frequency that is larger than that of the wall filter 1.
Example 2
Referring to fig. 3, the present embodiment provides a detection method of a doppler ultrasound blood flow detection device, including the following steps,
s1, preliminary judgment:
attenuating energy of the tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data) by a wall filter 1;
determining, by the autocorrelation processing module 1, at each spatial location of the ultrasound scan, the average velocity (Vel) and the energy (Pwr) using the data processed by the wall filter 1;
the blood flow detection module uses the smoothed average velocity (Vel), energy (Pwr) and B-mode image brightness (Env) to determine whether the location is tissue or blood flow, the determination logic is as follows
B-mode image brightness (Env), greater than a defined value for tissue and less than a defined value for blood flow;
average velocity (Vel), less than a defined value for tissue, greater than a defined value for blood flow;
energy (Pwr), less than a defined value for tissue, greater than a defined value for blood flow;
when all three values of the B-mode brightness (Env), the average speed (Vel) and the energy (Pwr) are judged to be inconsistent, setting a blood flow speed value (Vel 1) at the position to 0, and outputting a black-and-white signal representing the tissue;
and also comprises
S2, measurement of energy change rate (Pwr Chg):
when the blood flow detection module determines that the blood flow is the average velocity (Vel), the energy (Pwr) and the B-mode image brightness (Env) after the smoothing process, the energy change rate (Pwr Chg) is measured;
attenuating energy of a tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data) by a wall filter 2 having a cutoff frequency different from that of the wall filter 1;
the autocorrelation processing module 2 uses the data processed by the wall filter 2 to determine energy (Pwr 2);
the energy change rate processing module adopts energy (Pwr) and energy (Pwr 2) to determine the energy change rate (Pwr Chg) after the wall filter 1 and the wall filter 2 with different cut-off frequencies are processed, and the determination formula is that
S3, final judgment:
the blood flow detection module uses the energy change rate (Pwr Chg) to finally determine whether it is tissue or blood flow, and determines the blood flow velocity value (Vel 1), the determination logic of which is as follows,
the rate of energy change (Pwr Chg), greater than a defined value is tissue, less than a defined value is blood flow;
when it is determined that the tissue is a tissue, the blood flow velocity value (Vel 1) at the position is set to 0, and a black-and-white signal indicating the tissue is output; when it is determined that the blood flow is detected, the blood flow velocity value (Vel 1) at the position is set to the average velocity (Vel) after the smoothing process, and a color signal indicating the blood flow is outputted.
The method also comprises the following steps of,
s4, blood flow signal scan conversion processing: the scan conversion processing module performs scan conversion processing on a black-and-white signal representing tissue and a color signal representing blood flow, and converts the two signals into signals of rectangular coordinates or a polar coordinate system.
The method also comprises the following steps of,
s5, synthesizing and displaying blood flow and tissue signals: the display module superimposes the signals representing the tissues and the blood flow output by the scan conversion processing module on one frame of image for display.
In the step S1, the smoothing module 1 performs spatial and temporal smoothing on the average velocity (Vel) and the energy (Pwr) to remove noise therein;
in the step S2, the smoothing module 2 performs spatial and temporal smoothing on the energy (Pwr 2) to remove noise therein.
Description of examples 1 and 2:
as shown in fig. 4, given two sets of ultrasound doppler data with the same power spectrum as fig. 2, a wall filter 2 with a normalized cut-off frequency of 0.4 is passed. Then the average speed of the left signal is 0.5; on the right, the energy is relatively low because the filtering is done and the average velocity (Vel) is high, 0.65. If a conventional blood flow detection module is used to determine these two conditions, the left side would be correctly determined to be blood flow if the defined value of energy (Pwr) is set reasonably, while the right side would be correctly determined to be tissue because the energy is low. However, if only a wall filter 2 with a high cut-off frequency is provided, most of the blood flow energy is attenuated (as shown on the left side of fig. 4), which results in a significant decrease of the blood flow sensitivity of the ultrasound device.
The area of the closed region of the wavy line and the transverse axis represents energy. For the left signal, the calculated energy after filtering using the wall filter 2 is about 50% of the original blood flow energy, then the energy change rate (Pwr Chg) is about 50%; for the right signal, after filtering by using the wall filter 2, only noise remains after the tissue motion energy is completely filtered, and the energy is far lower than the original tissue motion energy, so the energy change rate (Pwr Chg) is close to 100%. It is apparent that the rate of change of the energy of the signals on the left and right sides is significantly different. The new parameter of the energy change rate (Pwr Chg) is sent to the blood flow detection module for comprehensive judgment, so that the error rate of blood flow detection can be obviously reduced.
In particular, a defined value, such as 70%, is set for the new parameter of energy change rate, and for signals detected as blood flow using conventional blood flow detection methods, the energy change rate (Pwr Chg) may be compared to the defined value of 70%, and if greater than a threshold, it is determined as tissue, and if less than the threshold, it is still determined as blood flow.
Therefore, the device adopts the new parameter of the energy change rate (Pwr Chg), which can increase the accuracy of detection and can not reduce the blood flow detection sensitivity of the ultrasonic equipment.
The above-described embodiments are intended to illustrate the present invention, not to limit it, and any modifications and variations made thereto fall within the spirit of the invention and the scope of the claims.
Claims (4)
1. A Doppler ultrasonic blood flow detection method comprises the following steps,
s1, preliminary judgment:
attenuating energy of the tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data) by a wall filter 1;
determining, by the autocorrelation processing module 1, at each spatial location of the ultrasound scan, the average velocity (Vel) and the energy (Pwr) using the data processed by the wall filter 1;
the blood flow detection module uses the smoothed average velocity (Vel), energy (Pwr) and B-mode image brightness (Env) to determine whether the location is tissue or blood flow, the determination logic is as follows
B-mode image brightness (Env), greater than a defined value for tissue and less than a defined value for blood flow;
average velocity (Vel), less than a defined value for tissue, greater than a defined value for blood flow;
energy (Pwr), less than a defined value for tissue, greater than a defined value for blood flow;
when all three values of the B-mode brightness (Env), the average speed (Vel) and the energy (Pwr) are judged to be inconsistent, setting a blood flow speed value (Vel 1) at the position to 0, and outputting a black-and-white signal representing the tissue;
characterized in that it also comprises
S2, measurement of energy change rate (Pwr Chg):
when the blood flow detection module determines that the blood flow is the average velocity (Vel), the energy (Pwr) and the B-mode image brightness (Env) after the smoothing process, the energy change rate (Pwr Chg) is measured;
attenuating energy of a tissue signal moving at a low speed in the quadrature-demodulated ultrasonic blood flow Data (iq_data) by a wall filter 2 having a cutoff frequency different from that of the wall filter 1;
the autocorrelation processing module 2 uses the data processed by the wall filter 2 to determine energy (Pwr 2);
the energy change rate processing module adopts energy (Pwr) and energy (Pwr 2) to determine the energy change rate (Pwr Chg) after the wall filter 1 and the wall filter 2 with different cut-off frequencies are processed, and the determination formula is that
；
The wall filter 1 and the wall filter 2 are both high-pass filters, and the cut-off frequency of the wall filter 2 is larger than that of the wall filter 1;
s3, final judgment:
the blood flow detection module uses the energy change rate (Pwr Chg) to finally determine whether it is tissue or blood flow, and determines the blood flow velocity value (Vel 1), the determination logic of which is as follows,
the rate of energy change (Pwr Chg), greater than a defined value is tissue, less than a defined value is blood flow;
when it is determined that the tissue is a tissue, the blood flow velocity value (Vel 1) at the position is set to 0, and a black-and-white signal indicating the tissue is output; when it is determined that the blood flow is detected, the blood flow velocity value (Vel 1) at the position is set to the average velocity (Vel) after the smoothing process, and a color signal indicating the blood flow is outputted.
2. The method for detecting a Doppler ultrasound blood flow detecting device according to claim 1, further comprising the steps of,
s4, blood flow signal scan conversion processing: the scan conversion processing module performs scan conversion processing on a black-and-white signal representing tissue and a color signal representing blood flow, and converts the two signals into signals of rectangular coordinates or a polar coordinate system.
3. The method for detecting a Doppler ultrasound blood flow detecting device according to claim 1, further comprising the steps of,
s5, synthesizing and displaying blood flow and tissue signals: the display module superimposes the signals representing the tissues and the blood flow output by the scan conversion processing module on one frame of image for display.
4. The detection method of the doppler ultrasound blood flow detection apparatus according to claim 1, wherein in step S1, the average velocity (Vel) and the energy (Pwr) are spatially and temporally smoothed by the smoothing module 1 to remove noise therein;
in step S2, the energy (Pwr 2) is spatially and temporally smoothed by the smoothing module 2 to remove noise therein.
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| CN1135712A (en) * | 1994-09-22 | 1996-11-13 | 勃勒柯研究有限公司 | Ultrasonic Spectral Contrast Imaging |
| CN1917814A (en) * | 2004-02-05 | 2007-02-21 | 皇家飞利浦电子股份有限公司 | Ultrasonic imaging of perfusion and blood flow with harmonic contrast agents |
| JP2005312773A (en) * | 2004-04-30 | 2005-11-10 | Toshiba Corp | Ultrasonic diagnostic equipment |
| JP2005318921A (en) * | 2004-05-06 | 2005-11-17 | Aloka Co Ltd | Ultrasonic diagnostic equipment |
| CN104883981A (en) * | 2013-01-23 | 2015-09-02 | 株式会社东芝 | Ultrasonic diagnostic device, image processing device, and image processing method |
| CN105590315A (en) * | 2015-12-04 | 2016-05-18 | 南京云石医疗科技有限公司 | Ultrasonic color Doppler image post-processing method |
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