Dual-frequency probe for bone imaging, imaging method of dual-frequency probe and medium

Abstract

The invention relates to the field of ultrasonic imaging, in particular to a dual-frequency probe for bone imaging, an imaging method of the dual-frequency probe and a medium, and the imaging method of the dual-frequency probe for bone imaging is characterized by comprising the following steps: S100, simultaneously transmitting a low-frequency sound wave signal and a high-frequency sound wave signal which are parallel through the dual-frequency probe; s200, receiving a reflected sound wave signal through a double-frequency probe, wherein the reflected sound wave signal comprises a high-frequency sound wave signal and a low-frequency sound wave signal; s300, separating the received reflection signal into a high-frequency signal and a low-frequency signal through a filtering technology; s400, directly applying a delay addition algorithm to independently add the high-frequency signal and the low-frequency signal which are subjected to delay processing, and generating an image according to the signals subjected to delay addition; s500, superposing the low-frequency image and the high-frequency image to obtain images for displaying the interiors of the superficial soft tissue and the skeleton at the same time; the advantages of the high-frequency image and the low-frequency image can be effectively combined, and finally a fine and deep clear fusion image is obtained.

Description

Technical Field

[0001] The invention relates to the field of ultrasonic imaging, and in particular to a dual-frequency probe for bone imaging and an imaging method thereof. Background Art

[0002] Medical ultrasound equipment uses ultrasound technology to obtain images or information about the internal structures of the human body. This probe is usually made of high-precision piezoelectric materials and can transmit and receive ultrasonic signals. Through the reflection and propagation time of these signals, doctors can observe dynamic images of the internal organs of the human body in real time, thereby diagnosing diseases and evaluating treatment.

[0003] In addition, ultrasound technology has demonstrated the advantages of high frame rate real-time imaging, providing doctors with key anatomical information updates and real-time tracking functions. Since the high-frequency sound waves emitted by the high-frequency probes of current medical ultrasound equipment have low penetration ability, they are suitable for imaging shallow soft tissues; they cannot see inside bones. Summary of the invention

[0004] The present invention provides a novel sound absorbing material and a preparation method thereof, and the technical problem to be solved is: how to make the probe generate low-frequency and high-frequency sound waves simultaneously, so as to simultaneously image the shallow soft tissue and the inside of the bone.

[0005] In order to achieve the above-mentioned object of the invention, the technical solution adopted by the present invention is:

[0006] In the first aspect, a dual-frequency probe for bone imaging includes a shell, a low-frequency positive electrode, a ground electrode, a high-frequency positive electrode, a low-frequency piezoelectric array, and a high-frequency piezoelectric array;

[0007] The low-frequency piezoelectric array and the high-frequency piezoelectric array are fixedly arranged in the shell. The direction in which the low-frequency piezoelectric array and the high-frequency piezoelectric array emit sound waves is the detection direction of the probe. When viewed along the detection direction of the probe, the low-frequency piezoelectric array and the high-frequency piezoelectric array are staggered.

[0008] The low-frequency piezoelectric array and the high-frequency piezoelectric array apply a low-frequency signal and a high-frequency signal respectively.

[0009] Furthermore, the ground electrode is located between the low-frequency piezoelectric array and the high-frequency piezoelectric array, and the negative electrodes of the low-frequency piezoelectric array and the high-frequency piezoelectric array are electrically connected to the ground electrode;

[0010] The low-frequency positive electrode and the high-frequency positive electrode are electrically connected to the positive electrodes of the low-frequency piezoelectric array and the high-frequency piezoelectric array respectively.

[0011] In a second aspect, an imaging method of a dual-frequency probe for bone imaging comprises the following steps:

[0012] S100, transmitting a low-frequency sound wave signal and a high-frequency sound wave signal in parallel simultaneously through a dual-frequency probe;

[0013] S200, receiving a reflected sound wave signal through a dual-frequency probe, wherein the reflected sound wave signal includes a high-frequency sound wave signal and a low-frequency sound wave signal;

[0014] S300, separating the received reflected signal into high-frequency and low-frequency signals by filtering technology;

[0015] S400, directly applying a delayed addition algorithm to separately add the delayed high-frequency signal and the low-frequency signal, and generating an image according to the delayed addition signal;

[0016] S500, superimposing the low-frequency image and the high-frequency image to obtain an image showing the shallow soft tissue and the inside of the bone at the same time.

[0017] Further, in step S300,

[0018] Step S310: performing noise filtering on the separated high-frequency signal and low-frequency signal to improve the signal-to-noise ratio.

[0019] Further, in step S320, time gain compensation is performed on the high-frequency signal and the low-frequency signal to correct the intensity change caused by signal attenuation; at the same time, the gain and phase of the high-frequency signal are adjusted and corrected respectively according to the data of sound wave attenuation and phase distortion caused by bones of low-frequency sound waves.

[0020] Further, step S400 also includes step S410, by identifying the soft tissue and bone areas of the low-frequency ultrasound image, and compensating for the signal distortion caused by the sound velocity difference and attenuation based on the uneven sound velocity or attenuation distribution, that is, making corresponding adjustments for each pixel point, so as to finally obtain a real low-frequency image that can accurately reflect the bones and soft tissues.

[0021] Furthermore, step S500 also includes step S510, in the spatial domain, higher weights are given to the high-frequency image and the low-frequency image in the soft tissue area and the bone area of ​​the image respectively; in the high-frequency image, the bone boundary is enhanced by the boundary operator, and in the low-frequency image, the internal structure of the bone is strengthened.

[0022] Furthermore, in step S520 after step S510, in the frequency domain, the frequency components of the high-frequency image and the low-frequency image are weightedly combined, and higher weights are respectively given to the high-frequency components of the high-frequency image and the low-frequency components of the low-frequency image, and finally a fused image is obtained by inverse Fourier transform.

[0023] Furthermore, when emitting sound waves, an emission delay is imposed on the array element so that the sound waves form a wavefront with a fixed deflection angle; by reconstructing images formed by sound waves in different directions and performing coherent or incoherent compounding, the overall imaging effect of the spine can be enhanced.

[0024] In a third aspect, a computer-readable storage medium stores a computer program, wherein the computer program, when executed by a processor, implements the steps of the imaging method of the dual-frequency probe for bone imaging as described in any one of claims 3 to 9.

[0025] The beneficial effects of the present invention are:

[0026] 1. The low-frequency positive electrode 20 and the high-frequency positive electrode 50 apply low-frequency and high-frequency voltage signals respectively, so that the low-frequency piezoelectric array 60 and the high-frequency piezoelectric array 70 generate parallel low-frequency and high-frequency sound waves respectively; so that the probe generates low-frequency and high-frequency sound waves at the same time, which is used to simultaneously image the shallow soft tissue and the inside of the bone.

[0027] 2. By applying different weights and image processing techniques in different depth areas, the advantages of high-frequency and low-frequency images can be effectively combined, and a fused image with both detailed and deep clarity can be obtained. This can better help doctors identify and analyze tissue structures during ultrasound examinations. BRIEF DESCRIPTION OF THE DRAWINGS

[0028] Figure 1 This is the main view of the dual-frequency probe;

[0029] Figure 2 for Figure 1 A top view of

[0030] Figure 3 A logic block diagram of an imaging method for a dual-frequency probe for bone imaging. DETAILED DESCRIPTION

[0031] In order to make the contents of the present invention more clearly understood, the technical solutions in the embodiments of the present invention are described clearly and completely.

[0032] See also Figure 1 , Figure 2 , a dual-frequency probe for bone imaging, comprising a housing 10, a low-frequency positive electrode 20, a ground electrode 30, a high-frequency positive electrode 50, a low-frequency piezoelectric array 60, and a high-frequency piezoelectric array 70;

[0033] The low-frequency piezoelectric array 60 and the high-frequency piezoelectric array 70 are fixedly disposed in the housing 10. The direction in which the low-frequency piezoelectric array 60 and the high-frequency piezoelectric array 70 emit sound waves is the detection direction of the probe; (See Figure 2 ) Viewed along the detection direction of the probe, the low-frequency piezoelectric array 60 and the high-frequency piezoelectric array 70 are staggered.

[0034] The ground electrode 30 is located between the low-frequency piezoelectric array 60 and the high-frequency piezoelectric array 70 , and the negative electrodes of the low-frequency piezoelectric array 60 and the high-frequency piezoelectric array 70 are electrically connected to the ground electrode 30 ;

[0035] The low-frequency positive electrode 20 and the high-frequency positive electrode 50 are electrically connected to the positive electrodes of the low-frequency piezoelectric array 60 and the high-frequency piezoelectric array 70 , respectively.

[0036] In summary, the low-frequency positive electrode 20 and the high-frequency positive electrode 50 apply low-frequency and high-frequency voltage signals respectively, so that the low-frequency piezoelectric array 60 and the high-frequency piezoelectric array 70 generate parallel low-frequency and high-frequency sound waves respectively; among them, the high-frequency sound wave decays faster in the medium and has a relatively short propagation distance, and is therefore suitable for imaging shallow soft tissues; the low-frequency sound wave signal has good penetration and is used for imaging deeper tissues, especially for imaging bone structures. Therefore, the probe is allowed to generate low-frequency and high-frequency sound waves at the same time to simultaneously image shallow soft tissues and the inside of bones.

[0037] On the other hand, an imaging method of a dual-frequency probe for bone imaging comprises the following steps:

[0038] S100, a dual-frequency probe is used to simultaneously transmit parallel low-frequency sound wave signals and high-frequency sound wave signals.

[0039] High-frequency sound waves decay faster in the medium and have a relatively short propagation distance, making them suitable for imaging shallow soft tissues; low-frequency sound wave signals have better penetration and are used for imaging deeper tissues, especially bone structures.

[0040] S200, receiving a reflected sound wave signal through a dual-frequency probe, wherein the reflected sound wave signal includes a high-frequency sound wave signal and a low-frequency sound wave signal;

[0041] S300, separating the received reflected signal into high-frequency and low-frequency signals by filtering technology;

[0042] Step S310: performing noise filtering on the separated high-frequency signal and low-frequency signal to improve the signal-to-noise ratio;

[0043] Step S320: Perform time gain compensation on the high-frequency signal and the low-frequency signal to correct the intensity change caused by signal attenuation. At the same time, adjust the gain and correct the phase of the high-frequency signal according to the data of the sound wave attenuation and phase distortion caused by the bone of the low-frequency sound wave.

[0044] Among them, phase distortion is: the different propagation speeds of sound waves in different media (such as soft tissue and bone) may cause the phase shift of the signal; this shift will affect the accuracy of the image and make the imaging result unclear.

[0045] S400 , directly applying a delayed addition algorithm to separately add the delayed high-frequency signal and the low-frequency signal, and generating an image according to the delayed addition signal.

[0046] Step S410, by identifying the soft tissue and bone areas of the low-frequency ultrasound image, and compensating for the signal distortion caused by the sound velocity difference and attenuation based on the uneven sound velocity or attenuation distribution, that is, making corresponding adjustments for each pixel point, so as to finally obtain a real low-frequency image that can accurately reflect the bones and soft tissues.

[0047] S500, superimposing the low-frequency image and the high-frequency image to obtain an image showing the shallow soft tissue and the inside of the bone at the same time.

[0048] Specifically, the following steps are included:

[0049] Step S510: In the spatial domain, higher weights are assigned to high-frequency images and low-frequency images in the soft tissue area and the bone area of ​​the image, respectively; in the high-frequency image, the bone boundary is enhanced by the boundary operator, and in the low-frequency image, the internal structure of the bone is enhanced. Among them, higher weights are assigned to high-frequency images in the soft tissue area of ​​the image, and higher weights are assigned to low-frequency images in the bone area of ​​the image, respectively utilizing the advantages of high-frequency sound waves and low-frequency sound waves to enhance the display effect of image fusion.

[0050] Step S520: In the frequency domain, the frequency components of the high-frequency image and the low-frequency image are weightedly combined, and higher weights are respectively given to the high-frequency components of the high-frequency image and the low-frequency components of the low-frequency image, and finally a fused image is obtained by inverse Fourier transform.

[0051] In summary, by applying different weights and image processing techniques in different depth areas, the advantages of high-frequency and low-frequency images can be effectively combined, and a fused image with both detailed and deep clarity can be obtained. This can better help doctors identify and analyze tissue structures during ultrasound examinations.

[0052] Furthermore, when emitting sound waves, an emission delay is imposed on the array element so that the sound waves form a wavefront with a fixed deflection angle; by reconstructing images formed by sound waves in different directions and performing coherent or incoherent compounding, the overall imaging effect of the spine can be enhanced.

[0053] In one embodiment of the present invention, a computer-readable storage medium is provided, wherein the computer-readable storage medium stores a computer program, and when the computer program is executed by a processor, the steps of the imaging method of the dual-frequency probe for bone imaging are implemented.

[0054] The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions and improvements made within the spirit and principles of the present invention shall be included in the protection scope of the present invention.

Claims

1. A dual-frequency probe for bone imaging, characterized in that: It includes a shell, a low-frequency positive electrode, a ground electrode, a high-frequency positive electrode, a low-frequency piezoelectric array, and a high-frequency piezoelectric array; The low-frequency piezoelectric array and the high-frequency piezoelectric array are fixedly arranged in the shell. The direction in which the low-frequency piezoelectric array and the high-frequency piezoelectric array emit sound waves is the detection direction of the probe. When viewed along the detection direction of the probe, the low-frequency piezoelectric array and the high-frequency piezoelectric array are staggered. The low-frequency piezoelectric array and the high-frequency piezoelectric array apply a low-frequency signal and a high-frequency signal respectively.

2. The dual-frequency probe for bone imaging according to claim 1, characterized in that: The ground electrode is located between the low-frequency piezoelectric array and the high-frequency piezoelectric array, and the negative electrodes of the low-frequency piezoelectric array and the high-frequency piezoelectric array are electrically connected to the ground electrode; The low-frequency positive electrode and the high-frequency positive electrode are electrically connected to the positive electrodes of the low-frequency piezoelectric array and the high-frequency piezoelectric array respectively.

3. An imaging method using a dual-frequency probe for bone imaging, characterized in that: The following steps are involved: S100, transmitting a low-frequency sound wave signal and a high-frequency sound wave signal in parallel simultaneously through a dual-frequency probe; S200, receiving a reflected sound wave signal through a dual-frequency probe, wherein the reflected sound wave signal includes a high-frequency sound wave signal and a low-frequency sound wave signal; S300, separating the received reflected signal into high-frequency and low-frequency signals by filtering technology; S400, directly applying a delayed addition algorithm to separately add the delayed high-frequency signal and the low-frequency signal, and generating an image according to the delayed addition signal; S500, superimposing the low-frequency image and the high-frequency image to obtain an image showing the shallow soft tissue and the inside of the bone at the same time.

4. The imaging method of the dual-frequency probe for bone imaging according to claim 3, characterized in that: In step S300, Step S310: performing noise filtering on the separated high-frequency signal and low-frequency signal to improve the signal-to-noise ratio.

5. The imaging method of the dual-frequency probe for bone imaging according to claim 4, characterized in that: Step S320, time gain compensation is performed on the high-frequency signal and the low-frequency signal to correct the intensity change caused by signal attenuation; at the same time, the gain and phase of the high-frequency signal are adjusted and corrected respectively according to the data of sound wave attenuation and phase distortion caused by bones of low-frequency sound waves.

6. The imaging method of the dual-frequency probe for bone imaging according to claim 3, characterized in that: Step S400 also includes step S410, which identifies the soft tissue and bone areas of the low-frequency ultrasound image and compensates for the signal distortion caused by the sound velocity difference and attenuation based on the uneven sound velocity or attenuation distribution, that is, makes corresponding adjustments for each pixel point, so that a real low-frequency image that can accurately reflect the bones and soft tissues is finally obtained.

7. The imaging method of the dual-frequency probe for bone imaging according to claim 3, characterized in that: Step S500 also includes step S510, in the spatial domain, higher weights are given to the high-frequency image and the low-frequency image in the soft tissue area and the bone area of ​​the image respectively; in the high-frequency image, the bone boundary is enhanced by the boundary operator, and in the low-frequency image, the internal structure of the bone is strengthened.

8. The imaging method of the dual-frequency probe for bone imaging according to claim 7, characterized in that: In step S520 after step S510, in the frequency domain, the frequency components of the high-frequency image and the low-frequency image are weightedly combined, and higher weights are respectively given to the high-frequency components of the high-frequency image and the low-frequency components of the low-frequency image, and finally a fused image is obtained by inverse Fourier transform.

9. The imaging method of the dual-frequency probe for bone imaging according to claim 3, characterized in that: When emitting sound waves, an emission delay is imposed on the array element so that the sound waves form a wavefront with a fixed deflection angle; by reconstructing the images formed by sound waves in different directions and performing coherent or incoherent compounding, the overall imaging effect of the spine can be enhanced.

10. A computer-readable storage medium storing a computer program, characterized in that: When the computer program is executed by a processor, the steps of the imaging method of the dual-frequency probe for bone imaging as described in any one of claims 3 to 9 are implemented.

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