CN117159023B - A method and device based on tissue harmonic imaging optimization - Google Patents
A method and device based on tissue harmonic imaging optimization Download PDFInfo
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Abstract
The invention provides a tissue harmonic imaging optimization method and device, which comprises the steps of S1, continuously sending pulses with the same pulse frequency and 180-degree phase difference in the medical detection imaging process to obtain pulse signals, S2, collecting voltage values of positive and negative pulses of the pulse signals, determining positive pulse areas and negative pulse areas based on positive pulse voltage absolute values, negative pulse voltage absolute values and pulse emission time lengths, S3, determining the type of complementary pulses and the number of complementary pulses based on area differences between the positive pulse areas and the negative pulse areas, S4, outputting and obtaining medical ultrasonic images based on the type of complementary pulses and the number of complementary pulses, optimizing the quality of harmonic imaging images by the method, eliminating influences on images caused by the differences of the positive and negative pulses, improving the imaging quality, facilitating diagnosis of doctors, and reducing risks of misjudgment of the doctors due to the image quality.
Description
Technical Field
The invention relates to the technical field of image processing, in particular to a tissue harmonic imaging optimization-based method and equipment.
Background
Ultrasonic imaging is generally used for a doctor to observe the internal tissue structure of a human body, and the doctor places a probe on the surface of skin corresponding to a part of the human body, so that an ultrasonic image of the part can be obtained. Ultrasonic imaging has become a primary auxiliary means for doctor diagnosis due to its safety, convenience, no damage, low cost, etc.
In the field of ultrasound imaging, harmonic imaging is used with better spatial resolution and contrast. Three methods for tissue harmonic extraction are commonly used, namely band-pass filtering imaging, pulse inversion harmonic imaging and pulse amplitude modulation harmonic imaging.
The invention optimizes based on the pulse inversion harmonic imaging principle, in the imaging process, by continuously transmitting two pulses, the pulse frequencies are consistent, the phase difference is 180 degrees, the received two pulse signals are added, after the addition, the fundamental wave and the odd harmonic are counteracted each other theoretically, and the even harmonic is doubled as the original one, so that the invention is enhanced. The positive pulse and the negative pulse have the same area, and the imaging effect is best when the addition can be just counteracted. However, in the practical application process, due to various factors such as non-linearity of the hardware of the ultrasonic system, some deviation is unavoidable between the pulse and the negative pulse, which can lead to the degradation of image quality and bring inconvenience to the diagnosis of doctors.
Disclosure of Invention
The invention provides a tissue harmonic imaging optimization-based method and tissue harmonic imaging optimization-based equipment, which are used for solving the problems in the background technology.
A method of tissue harmonic imaging optimization comprising:
s1, continuously transmitting pulses with the same pulse frequency and 180-degree phase difference in the medical detection imaging process to obtain pulse signals;
s2, collecting voltage values of positive and negative pulses of a pulse signal, and determining positive pulse area and negative pulse area based on the positive pulse voltage absolute value, the negative pulse voltage absolute value and the pulse emission time length;
s3, determining the type and the number of the supplementary pulses based on the area difference between the positive pulse area and the negative pulse area;
and S4, outputting and obtaining a medical ultrasonic image based on the type and the number of the supplementary pulses.
Preferably, the method for determining the pulse frequency in S1 is as follows:
Determining medical diagnosis precision based on the medical diagnosis features, and determining image precision of the medical ultrasonic image according to the medical diagnosis precision;
the pulse frequency is determined based on a correlation between the pulse frequency and the image accuracy.
Preferably, in S2, collecting a voltage value of positive and negative pulses of the pulse signal includes:
Determining the acquisition granularity preset by the analog front-end chip, and determining the number of the acquisition granularity;
Distributing sampling channels of an analog front-end chip for the pulse signals based on the acquisition granularity and the corresponding quantity thereof;
and collecting positive and negative pulses of the pulse signals according to the distributed sampling channels, and determining the voltage values of the positive and negative pulses according to the collecting results.
In this embodiment, the acquisition granularity is the period of acquisition of the pulse signal.
Preferably, in S2, determining the positive pulse area and the negative pulse area based on the positive pulse voltage absolute value, the negative pulse voltage absolute value, and the pulse transmission time length includes:
taking the product of the absolute value of the positive pulse voltage and the pulse transmitting time length as the positive pulse area;
the product of the absolute value of the negative pulse voltage and the pulse emission time length is taken as the negative pulse area.
Preferably, in S3, determining the type of supplemental pulse and the number of supplemental pulses based on the area difference between the positive pulse area and the negative pulse area includes:
judging whether the area difference between the positive pulse area and the negative pulse area is equal to zero or not;
if yes, determining that pulse supplementation is not needed;
Otherwise, determining that pulse supplementation is required, determining that the supplementation pulse type is negative pulse supplementation when the area difference between the positive pulse area and the negative pulse area is larger than zero, otherwise, determining that the supplementation pulse type is positive pulse supplementation;
based on the absolute value of the area difference, the pulse replenishment number under the replenishment pulse type is determined.
Preferably, determining the pulse replenishment number under the replenishment pulse type based on the area difference absolute value includes:
when the type of the supplementary pulse is determined to be positive pulse supplementary, the number of the supplementary positive pulses is the ratio of the absolute value of the area difference value to the absolute value of the positive pulse voltage, and the integral value is upwards rounded;
When the type of the supplementary pulse is determined to be negative pulse supplementary, the number of supplementary negative pulses is a rounded up value of the ratio of the absolute value of the area difference to the absolute value of the negative pulse voltage.
Preferably, in S4, outputting the obtained medical ultrasound image based on the type of the supplemental pulse and the number of the supplemental pulses includes:
Adding compensation pulse signals according to the type and the number of the compensation pulses in the process of imaging by using the pulse signals to obtain ultrasonic image data;
And evaluating the imaging quality based on the ultrasonic image data, correcting the subsequent imaging process by using the pulse signals according to the evaluation result, and finally obtaining the medical ultrasonic image.
Preferably, the sampling channels of the analog front end chip are allocated based on the acquisition granularity and the corresponding number thereof, including:
Determining the number of sampling channels of an analog front-end chip;
Based on the acquisition granularity and the corresponding quantity thereof, taking the acquisition granularity as a unit, matching all the acquisition granularity with corresponding sampling channels for pulse signals according to the sequence, and obtaining a first matching result;
Determining a first sampling channel corresponding to the positive pulse and a second sampling channel corresponding to the pulse based on the first matching result, and judging whether the channel sampling characteristics in the first sampling channel are consistent with the channel sampling characteristics in the second sampling channel;
if so, distributing sampling channels of the analog front-end chip for the pulse signals based on the first matching result;
Otherwise, the first matching result is adjusted based on the characteristic difference of the channel sampling characteristics in the first sampling channel and the channel sampling characteristics in the second sampling channel to obtain a second matching result, and the sampling channel of the analog front-end chip is allocated to the pulse signal based on the second matching result.
Preferably, the adjusting the first matching result based on the characteristic difference between the channel sampling characteristic in the first sampling channel and the channel sampling characteristic in the second sampling channel to obtain a second matching result includes:
Determining a channel selection difference and a sampling interval difference from the characteristic difference, performing first adjustment on channel self allocation in a first matching result based on the channel selection difference, and performing second adjustment on channel allocation sequence in the first matching result based on the sampling interval difference;
and obtaining a second matching result based on the first adjustment and the second adjustment.
Preferably, the imaging quality is evaluated based on the ultrasound image data, and the subsequent imaging process using the pulse signal is corrected according to the evaluation result, so as to finally obtain a medical ultrasound image, which comprises:
Based on standard ultrasonic image data corresponding to the standard medical ultrasonic image, evaluating the imaging quality based on the ultrasonic image data to obtain an evaluation result;
Judging whether the ultrasonic image data meets the medical diagnosis requirement or not based on the evaluation result;
if yes, the subsequent pulse signal imaging process is not corrected;
Otherwise, determining correction characteristics according to abnormal ultrasonic image data which does not meet medical diagnosis requirements in the evaluation result, and correcting a follow-up pulse signal imaging process based on the correction characteristics to finally obtain a medical ultrasonic image.
Preferably, an apparatus for tissue harmonic imaging optimization comprises:
the pulse transmitting module is used for continuously transmitting pulses with the same pulse frequency and 180-degree phase difference in the medical detection imaging process to obtain pulse signals;
the pulse analysis module is used for collecting the voltage values of positive and negative pulses of the pulse signals and determining positive pulse areas and negative pulse areas based on the positive pulse voltage absolute value, the negative pulse voltage absolute value and the pulse emission time length;
A number determination module for determining a supplemental pulse type and a supplemental pulse number based on an area difference between the positive pulse area and the negative pulse area;
And the supplementary output module is used for outputting and obtaining medical ultrasonic images based on the supplementary pulse types and the supplementary pulse quantity.
Compared with the prior art, the invention has the following beneficial effects:
In the medical detection imaging process, pulses with the same pulse frequency and 180-degree phase difference are continuously transmitted to obtain pulse signals to realize pulse inversion harmonic imaging, a basis is provided for acquiring medical ultrasonic images, then the voltage values of positive and negative pulses of the pulse signals are acquired, the positive pulse area and the negative pulse area are determined based on the positive pulse voltage absolute value, the negative pulse voltage absolute value and the pulse transmitting time length, the supplementary pulse type and the supplementary pulse quantity are determined based on the area difference between the positive pulse area and the negative pulse area, and the medical ultrasonic images are output and obtained based on the supplementary pulse type and the supplementary pulse quantity.
Additional features and advantages of the invention will be set forth in the description which follows, and in part will be obvious from the description, or may be learned by practice of the invention. The objectives and other advantages of the invention will be realized and attained by the structure particularly pointed out in the written description and claims thereof as well as the appended drawings.
The technical scheme of the invention is further described in detail through the drawings and the embodiments.
Drawings
The accompanying drawings are included to provide a further understanding of the invention and are incorporated in and constitute a part of this specification, illustrate the invention and together with the embodiments of the invention, serve to explain the invention. In the drawings:
FIG. 1 is a flow chart of a method for tissue harmonic imaging optimization in accordance with an embodiment of the present invention;
FIG. 2 is a flow chart of voltage value acquisition of positive and negative pulses in an embodiment of the invention;
FIG. 3 is a flow chart of outputting a medical ultrasound image in an embodiment of the present invention;
fig. 4 is a block diagram of an apparatus based on tissue harmonic imaging optimization in an embodiment of the invention.
Detailed Description
The preferred embodiments of the present invention will be described below with reference to the accompanying drawings, it being understood that the preferred embodiments described herein are for illustration and explanation of the present invention only, and are not intended to limit the present invention.
Example 1:
an embodiment of the present invention provides a method for optimizing tissue harmonic imaging, as shown in fig. 1, including:
s1, continuously transmitting pulses with the same pulse frequency and 180-degree phase difference in the medical detection imaging process to obtain pulse signals;
s2, collecting voltage values of positive and negative pulses of a pulse signal, and determining positive pulse area and negative pulse area based on the positive pulse voltage absolute value, the negative pulse voltage absolute value and the pulse emission time length;
s3, determining the type and the number of the supplementary pulses based on the area difference between the positive pulse area and the negative pulse area;
and S4, outputting and obtaining a medical ultrasonic image based on the type and the number of the supplementary pulses.
In this embodiment, the supplemental pulse type is either positive pulse compensation or negative pulse compensation.
In this embodiment, the product of the absolute value of the voltage and the pulse-emission time length is the pulse area.
The method has the advantages that pulses with the same pulse frequency and 180-degree phase difference are continuously transmitted in the medical detection imaging process, pulse signals are obtained to achieve pulse inversion harmonic imaging, a basis is provided for obtaining medical ultrasonic images, then voltage values of positive and negative pulses of the pulse signals are collected, positive pulse areas and negative pulse areas are determined based on positive pulse voltage absolute values, negative pulse voltage absolute values and pulse emission time lengths, and the type and the number of complementary pulses are determined based on area differences between the positive pulse areas and the negative pulse areas, and medical ultrasonic images are obtained based on the type and the number of complementary pulses.
Example 2:
based on embodiment 1, the embodiment of the invention provides a method based on tissue harmonic imaging optimization, and the method for determining the pulse frequency in S1 is as follows:
Determining medical diagnosis precision based on the medical diagnosis features, and determining image precision of the medical ultrasonic image according to the medical diagnosis precision;
the pulse frequency is determined based on a correlation between the pulse frequency and the image accuracy.
The design scheme has the beneficial effects that the medical diagnosis precision is determined according to the medical diagnosis characteristics, the image precision of the medical ultrasonic image is determined according to the medical diagnosis precision, and the pulse frequency is determined based on the correlation between the pulse frequency and the image precision, so that the image quality of the medical ultrasonic image obtained under the pulse frequency meets the medical diagnosis requirement.
Example 3:
Based on embodiment 1, the embodiment of the present invention provides a method for optimizing imaging based on tissue harmonic, as shown in fig. 2, in S2, collecting voltage values of positive and negative pulses of a pulse signal, including:
Determining the acquisition granularity preset by the analog front-end chip, and determining the number of the acquisition granularity;
Distributing sampling channels of an analog front-end chip for the pulse signals based on the acquisition granularity and the corresponding quantity thereof;
and collecting positive and negative pulses of the pulse signals according to the distributed sampling channels, and determining the voltage values of the positive and negative pulses according to the collecting results.
In this embodiment, the acquisition granularity is the period of acquisition of the pulse signal.
In this embodiment, the total number of acquisition granularity is accumulated to achieve the acquisition of the total pulse echo signal.
In this embodiment, the analog front end chip capital contains multiple sampling channels.
The design scheme has the advantages that sampling channels of the analog front end chip are distributed for the pulse signals based on the collection granularity and the corresponding number of the sampling channels, positive and negative pulses of the pulse signals are collected according to the distributed sampling channels, voltage values of the positive and negative pulses are determined according to collection results, sampling errors are reduced, and accuracy of the voltage values of the positive and negative pulses is guaranteed.
Example 4:
Based on embodiment 1, the embodiment of the invention provides a method based on tissue harmonic imaging optimization, in S2, based on positive pulse voltage absolute value, negative pulse voltage absolute value and pulse transmitting time length, positive pulse area and negative pulse area are determined, including:
taking the product of the absolute value of the positive pulse voltage and the pulse transmitting time length as the positive pulse area;
the product of the absolute value of the negative pulse voltage and the pulse emission time length is taken as the negative pulse area.
The design scheme has the advantages that the product of the absolute value of the positive pulse voltage and the pulse transmitting time length is used as a positive pulse area, and the product of the absolute value of the negative pulse voltage and the pulse transmitting time length is used as a negative pulse area. The acquisition of the pulse area is realized.
Example 5:
Based on embodiment 1, an embodiment of the present invention provides a method for optimizing imaging based on tissue harmonic, in S3, determining a type of supplemental pulse and a number of supplemental pulses based on an area difference between a positive pulse area and a negative pulse area, including:
judging whether the area difference between the positive pulse area and the negative pulse area is equal to zero or not;
if yes, determining that pulse supplementation is not needed;
Otherwise, determining that pulse supplementation is required, determining that the supplementation pulse type is negative pulse supplementation when the area difference between the positive pulse area and the negative pulse area is larger than zero, otherwise, determining that the supplementation pulse type is positive pulse supplementation;
based on the absolute value of the area difference, the pulse replenishment number under the replenishment pulse type is determined.
The design scheme has the beneficial effects that the supplementary pulse type is determined by judging the area difference between the positive pulse area and the negative pulse area and the size of zero, and the pulse supplementary quantity under the supplementary pulse type is determined based on the absolute value of the area difference, so that the optimization of the harmonic imaging image quality is realized, the influence of the difference of the positive pulse and the negative pulse on the image is eliminated, and the imaging quality is improved.
Example 6:
Based on embodiment 5, an embodiment of the present invention provides a method for optimizing imaging based on tissue harmonic, determining a pulse replenishment number under a replenishment pulse type based on an absolute value of an area difference, including:
when the type of the supplementary pulse is determined to be positive pulse supplementary, the number of the supplementary positive pulses is the ratio of the absolute value of the area difference value to the absolute value of the positive pulse voltage, and the integral value is upwards rounded;
When the type of the supplementary pulse is determined to be negative pulse supplementary, the number of supplementary negative pulses is a rounded up value of the ratio of the absolute value of the area difference to the absolute value of the negative pulse voltage.
The design scheme has the beneficial effects of providing a determination mode for determining the pulse replenishment quantity under the replenishment pulse type and providing a data basis for image optimization.
Example 7:
Based on embodiment 1, an embodiment of the present invention provides a method for optimizing imaging based on tissue harmonic, as shown in fig. 3, in S4, based on a type of supplemental pulse and a number of supplemental pulses, outputting and obtaining a medical ultrasound image, including:
Adding compensation pulse signals according to the type and the number of the compensation pulses in the process of imaging by using the pulse signals to obtain ultrasonic image data;
And evaluating the imaging quality based on the ultrasonic image data, correcting the subsequent imaging process by using the pulse signals according to the evaluation result, and finally obtaining the medical ultrasonic image.
The beneficial effects of the design scheme are that the ultrasound image data are obtained by adding the compensation pulse signals according to the type and the number of the compensation pulses in the process of imaging by using the pulse signals;
Evaluating the imaging quality based on the ultrasonic image data, correcting the subsequent imaging process by using the pulse signals according to the evaluation result, finally obtaining a medical ultrasonic image, the method can optimize the harmonic imaging image quality, eliminate the influence of the difference of positive and negative pulses on the image, improve the imaging quality, facilitate the diagnosis of doctors and reduce the risk of erroneous judgment of the doctors caused by the image quality.
Example 8:
Based on embodiment 3, the embodiment of the invention provides a method for optimizing imaging based on tissue harmonic, which allocates sampling channels of an analog front-end chip based on acquisition granularity and corresponding quantity thereof, and comprises the following steps:
Determining the number of sampling channels of an analog front-end chip;
Based on the acquisition granularity and the corresponding quantity thereof, taking the acquisition granularity as a unit, matching all the acquisition granularity with corresponding sampling channels for pulse signals according to the sequence, and obtaining a first matching result;
Determining a first sampling channel corresponding to the positive pulse and a second sampling channel corresponding to the pulse based on the first matching result, and judging whether the channel sampling characteristics in the first sampling channel are consistent with the channel sampling characteristics in the second sampling channel;
if so, distributing sampling channels of the analog front-end chip for the pulse signals based on the first matching result;
Otherwise, the first matching result is adjusted based on the characteristic difference of the channel sampling characteristics in the first sampling channel and the channel sampling characteristics in the second sampling channel to obtain a second matching result, and the sampling channel of the analog front-end chip is allocated to the pulse signal based on the second matching result.
In this embodiment, the sampling channels corresponding to the pulse signal matching are numbered for all the acquisition granularity in order, and the channels are provided for the acquisition granularity in order according to the numbering order.
The design scheme has the advantages that the first matching result is obtained by matching all the acquisition granularity with the corresponding sampling channels of the pulse signals according to the sequence, the distribution of the sampling channels is achieved, then the first sampling channels corresponding to positive pulses and the second sampling channels corresponding to the pulses are determined based on the first matching result, whether the channel sampling characteristics in the first sampling channels are consistent with the channel sampling characteristics in the second sampling channels is judged, if yes, the sampling channels of the analog front-end chip are distributed for the pulse signals based on the first matching result, otherwise, the second matching result is obtained by adjusting the first matching result based on the characteristic difference of the channel sampling characteristics in the first sampling channels and the channel sampling characteristics in the second sampling channels, the sampling channels of the analog front-end chip are distributed for the pulse signals based on the second matching result, the accurate distribution of the sampling channels is achieved, and a basis is provided for achieving accurate acquisition of pulse voltage values.
Example 9:
Based on embodiment 8, the embodiment of the invention provides a method based on tissue harmonic imaging optimization, which adjusts a first matching result based on a characteristic difference between a channel sampling characteristic in a first sampling channel and a channel sampling characteristic in a second sampling channel to obtain a second matching result, and comprises the following steps:
Determining a channel selection difference and a sampling interval difference from the characteristic difference, performing first adjustment on channel self allocation in a first matching result based on the channel selection difference, and performing second adjustment on channel allocation sequence in the first matching result based on the sampling interval difference;
and obtaining a second matching result based on the first adjustment and the second adjustment.
In this embodiment, the channel selection difference is that the channel selection ratio between the positive and negative pulses is unequal, which affects the acquisition accuracy.
In this embodiment, the sampling interval difference is a difference in channel acquisition order between positive and negative pulses, and the order imbalance also affects the acquisition accuracy.
The design scheme has the advantages that channel selection differences and sampling interval differences are determined from the characteristic differences, channel distribution in the first matching result is subjected to first adjustment based on the channel selection differences, channel distribution sequence in the first matching result is subjected to second adjustment based on the sampling interval differences, the second matching result is obtained based on the first adjustment and the second adjustment, accurate distribution of sampling channels is achieved, and basis is provided for accurate collection of pulse voltage values.
Example 10:
based on embodiment 7, the embodiment of the invention provides a method based on tissue harmonic imaging optimization, which evaluates imaging quality based on ultrasonic image data, corrects a subsequent imaging process by using a pulse signal according to an evaluation result, and finally obtains a medical ultrasonic image, and comprises the following steps:
Based on standard ultrasonic image data corresponding to the standard medical ultrasonic image, evaluating the imaging quality based on the ultrasonic image data to obtain an evaluation result;
Judging whether the ultrasonic image data meets the medical diagnosis requirement or not based on the evaluation result;
if yes, the subsequent pulse signal imaging process is not corrected;
Otherwise, determining correction characteristics according to abnormal ultrasonic image data which does not meet medical diagnosis requirements in the evaluation result, and correcting a follow-up pulse signal imaging process based on the correction characteristics to finally obtain a medical ultrasonic image.
In this embodiment, the subsequent correction with the pulse signal imaging process is performed based on the correction feature, for example, correction in a pulse voltage value determination manner, and correction in a pulse area calculation process.
The design scheme has the advantages that based on standard ultrasonic image data corresponding to standard medical ultrasonic images, imaging quality is evaluated based on the ultrasonic image data to obtain an evaluation result, whether the ultrasonic image data meets medical diagnosis requirements is judged based on the evaluation result, if yes, the follow-up pulse signal imaging process is not corrected, otherwise, correction characteristics are determined according to abnormal ultrasonic image data which does not meet the medical diagnosis requirements in the evaluation result, the follow-up pulse signal imaging process is corrected based on the correction characteristics, the medical ultrasonic image is finally obtained, optimization of the medical ultrasonic image is achieved in a mode of evaluating and correcting simultaneously, imaging quality is improved, diagnosis by doctors is facilitated, and misjudgment risks of doctors due to the image quality are reduced.
Example 11:
Based on the method of tissue harmonic imaging optimization of any of embodiments 1-10, there is provided an apparatus for tissue harmonic imaging optimization, as shown in fig. 4, comprising:
the pulse transmitting module is used for continuously transmitting pulses with the same pulse frequency and 180-degree phase difference in the medical detection imaging process to obtain pulse signals;
the pulse analysis module is used for collecting the voltage values of positive and negative pulses of the pulse signals and determining positive pulse areas and negative pulse areas based on the positive pulse voltage absolute value, the negative pulse voltage absolute value and the pulse emission time length;
A number determination module for determining a supplemental pulse type and a supplemental pulse number based on an area difference between the positive pulse area and the negative pulse area;
And the supplementary output module is used for outputting and obtaining medical ultrasonic images based on the supplementary pulse types and the supplementary pulse quantity.
In this embodiment, the supplemental pulse type is either positive pulse compensation or negative pulse compensation.
In this embodiment, the product of the absolute value of the voltage and the pulse-emission time length is the pulse area.
In this embodiment, the apparatus for tissue harmonic imaging optimization further includes a pulse receiving module, configured to receive the pulse signal obtained by the pulse transmitting module, process the pulse signal by the signal processing module, and send the pulse signal to the pulse analyzing module for signal analysis, and further includes an image display module, configured to display the medical ultrasound image obtained by the complementary output module, where, for the sake of the integrity of the apparatus, the pulse receiving module, the signal processing module and the complementary output module are conventional necessary design features of the ultrasound apparatus, and are explained herein.
The method has the advantages that pulses with the same pulse frequency and 180-degree phase difference are continuously transmitted in the medical detection imaging process, pulse signals are obtained to achieve pulse inversion harmonic imaging, a basis is provided for obtaining medical ultrasonic images, then voltage values of positive and negative pulses of the pulse signals are collected, positive pulse areas and negative pulse areas are determined based on positive pulse voltage absolute values, negative pulse voltage absolute values and pulse emission time lengths, and the type and the number of complementary pulses are determined based on area differences between the positive pulse areas and the negative pulse areas, and medical ultrasonic images are obtained based on the type and the number of complementary pulses.
It will be apparent to those skilled in the art that various modifications and variations can be made to the present invention without departing from the spirit or scope of the invention. Thus, it is intended that the present invention also include such modifications and alterations insofar as they come within the scope of the appended claims or the equivalents thereof.
Claims (10)
1. A method of tissue harmonic imaging optimization comprising:
s1, continuously transmitting pulses with the same pulse frequency and 180-degree phase difference in the medical detection imaging process to obtain pulse signals;
s2, collecting voltage values of positive and negative pulses of a pulse signal, and determining positive pulse area and negative pulse area based on the positive pulse voltage absolute value, the negative pulse voltage absolute value and the pulse emission time length;
s3, determining the type and the number of the supplementary pulses based on the area difference between the positive pulse area and the negative pulse area;
s4, outputting and obtaining a medical ultrasonic image based on the type and the number of the supplementary pulses;
in S4, outputting a medical ultrasound image based on the type of the supplemental pulse and the number of the supplemental pulses, including:
Adding compensation pulse signals according to the type and the number of the compensation pulses in the process of imaging by using the pulse signals to obtain ultrasonic image data;
And evaluating the imaging quality based on the ultrasonic image data, correcting the subsequent imaging process by using the pulse signals according to the evaluation result, and finally obtaining the medical ultrasonic image.
2. A method of tissue harmonic imaging optimization according to claim 1, characterized in that the pulse frequency in S1 is determined as follows:
Determining medical diagnosis precision based on the medical diagnosis features, and determining image precision of the medical ultrasonic image according to the medical diagnosis precision;
the pulse frequency is determined based on a correlation between the pulse frequency and the image accuracy.
3. The method of tissue harmonic imaging optimization of claim 1, wherein in S2, collecting voltage values of positive and negative pulses of the pulse signal comprises:
Determining the acquisition granularity preset by the analog front-end chip, and determining the number of the acquisition granularity;
Distributing sampling channels of an analog front-end chip for the pulse signals based on the acquisition granularity and the corresponding quantity thereof;
and collecting positive and negative pulses of the pulse signals according to the distributed sampling channels, and determining the voltage values of the positive and negative pulses according to the collecting results.
4. The method of tissue harmonic imaging optimization of claim 1, wherein determining positive and negative pulse areas based on positive pulse voltage absolute values, negative pulse voltage absolute values, and pulse transmission time lengths in S2 comprises:
taking the product of the absolute value of the positive pulse voltage and the pulse transmitting time length as the positive pulse area;
the product of the absolute value of the negative pulse voltage and the pulse emission time length is taken as the negative pulse area.
5. The method of tissue harmonic imaging optimization of claim 1, wherein in S3, determining the supplemental pulse type and the number of supplemental pulses based on the area difference between the positive pulse area and the negative pulse area comprises:
judging whether the area difference between the positive pulse area and the negative pulse area is equal to zero or not;
if yes, determining that pulse supplementation is not needed;
Otherwise, determining that pulse supplementation is required, determining that the supplementation pulse type is negative pulse supplementation when the area difference between the positive pulse area and the negative pulse area is larger than zero, otherwise, determining that the supplementation pulse type is positive pulse supplementation;
based on the absolute value of the area difference, the pulse replenishment number under the replenishment pulse type is determined.
6. The method of tissue harmonic imaging optimization of claim 5, wherein determining the number of pulse supplements under the type of supplemental pulses based on the absolute value of the area difference comprises:
when the type of the supplementary pulse is determined to be positive pulse supplementary, the number of the supplementary positive pulses is the ratio of the absolute value of the area difference value to the absolute value of the positive pulse voltage, and the integral value is upwards rounded;
When the type of the supplementary pulse is determined to be negative pulse supplementary, the number of supplementary negative pulses is a rounded up value of the ratio of the absolute value of the area difference to the absolute value of the negative pulse voltage.
7. A method of tissue harmonic imaging optimization as claimed in claim 3, wherein assigning sampling channels of an analog front end chip based on acquisition granularity and its corresponding number comprises:
Determining the number of sampling channels of an analog front-end chip;
Based on the acquisition granularity and the corresponding quantity thereof, taking the acquisition granularity as a unit, matching all the acquisition granularity with corresponding sampling channels for pulse signals according to the sequence, and obtaining a first matching result;
Determining a first sampling channel corresponding to the positive pulse and a second sampling channel corresponding to the pulse based on the first matching result, and judging whether the channel sampling characteristics in the first sampling channel are consistent with the channel sampling characteristics in the second sampling channel;
if so, distributing sampling channels of the analog front-end chip for the pulse signals based on the first matching result;
Otherwise, the first matching result is adjusted based on the characteristic difference of the channel sampling characteristics in the first sampling channel and the channel sampling characteristics in the second sampling channel to obtain a second matching result, and the sampling channel of the analog front-end chip is allocated to the pulse signal based on the second matching result.
8. The method of tissue harmonic imaging optimization of claim 7, wherein adjusting the first matching result based on a difference in characteristics of the channel sampling features in the first sampling channel and the channel sampling features in the second sampling channel to obtain the second matching result comprises:
Determining a channel selection difference and a sampling interval difference from the characteristic difference, performing first adjustment on channel self allocation in a first matching result based on the channel selection difference, and performing second adjustment on channel allocation sequence in the first matching result based on the sampling interval difference;
and obtaining a second matching result based on the first adjustment and the second adjustment.
9. The method of tissue harmonic imaging optimization of claim 1, wherein the evaluating the imaging quality based on the ultrasound image data and correcting the subsequent imaging procedure using the pulse signal based on the evaluation result to obtain the medical ultrasound image comprises:
Based on standard ultrasonic image data corresponding to the standard medical ultrasonic image, evaluating the imaging quality based on the ultrasonic image data to obtain an evaluation result;
Judging whether the ultrasonic image data meets the medical diagnosis requirement or not based on the evaluation result;
if yes, the subsequent pulse signal imaging process is not corrected;
Otherwise, determining correction characteristics according to abnormal ultrasonic image data which does not meet medical diagnosis requirements in the evaluation result, and correcting a follow-up pulse signal imaging process based on the correction characteristics to finally obtain a medical ultrasonic image.
10. A method of tissue harmonic imaging optimization-based method according to any one of claims 1-9, providing a tissue harmonic imaging optimization-based apparatus comprising:
the pulse transmitting module is used for continuously transmitting pulses with the same pulse frequency and 180-degree phase difference in the medical detection imaging process to obtain pulse signals;
the pulse analysis module is used for collecting the voltage values of positive and negative pulses of the pulse signals and determining positive pulse areas and negative pulse areas based on the positive pulse voltage absolute value, the negative pulse voltage absolute value and the pulse emission time length;
A number determination module for determining a supplemental pulse type and a supplemental pulse number based on an area difference between the positive pulse area and the negative pulse area;
And the supplementary output module is used for outputting and obtaining medical ultrasonic images based on the supplementary pulse types and the supplementary pulse quantity.
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| US5632277A (en) * | 1996-06-28 | 1997-05-27 | Siemens Medical Systems, Inc. | Ultrasound imaging system employing phase inversion subtraction to enhance the image |
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| JP5247958B2 (en) * | 2001-06-13 | 2013-07-24 | 株式会社東芝 | Ultrasonic diagnostic apparatus and ultrasonic echo signal processing method |
| CN101264022B (en) * | 2007-03-16 | 2012-01-11 | 通用电气公司 | Method and system for accurately evaluating time delay in ultrasonic imaging |
| TW200922528A (en) * | 2007-11-20 | 2009-06-01 | Univ Nat Taiwan Science Tech | Method and apparatus for modifying ultrasonic tissue harmonic amplitude |
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| JP2014233402A (en) * | 2013-05-31 | 2014-12-15 | 富士フイルム株式会社 | Ultrasonic diagnostic apparatus, sound-ray signal generation method for ultrasonic diagnostic apparatus, and sound-ray signal generating program for ultrasonic diagnostic apparatus |
| CN104188685B (en) * | 2014-09-28 | 2016-05-11 | 飞依诺科技(苏州)有限公司 | Ultrasonic contrast imaging method and system based on amplitude modulation(PAM) in transmitted pulse |
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