CN114344741A - Focused ultrasound system, method for determining imaging parameters, control method, and medium - Google Patents
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Abstract
The invention provides a method for determining imaging parameters of a focused ultrasound system, which comprises the following steps: acquiring an ultrasonic image; identifying the position of the skin edge in the ultrasonic image; determining the distance between the skin and the ultrasonic probe according to the position of the skin edge in the ultrasonic image; and determining the current imaging parameters of the focused ultrasound system according to the distance between the skin and the ultrasound probe. The present disclosure also provides a control method of a focused ultrasound system, an image processing apparatus, a controller, a focused ultrasound system, and a computer readable medium.
Description
Technical Field
The present invention relates to the field of medical equipment, and in particular, to a method of determining imaging parameters of a focused ultrasound system, a method of controlling a focused ultrasound system, an image processing apparatus, a controller, a focused ultrasound system, and a computer readable medium.
Background
During the treatment of tumors by Focused Ultrasound (FUS) Surgery, real-time image monitoring is required. The B-ultrasonic or color ultrasonic can be used for image monitoring, but the ultrasonic equipment on the market is used for diagnosis and not for monitoring and positioning in the tumor treatment process.
When the ultrasonic equipment is used for diagnosis, the couplant with the acoustic characteristics similar to those of human tissues is used, the ultrasonic probe is tightly attached to the skin, and imaging parameters do not need to be adjusted after the imaging parameters are adjusted.
However, when the FUS is used to treat tumor, pure water is used as a medium instead of the coupling agent, the distance between the probe and the skin is constantly changed, and the imaging parameters also need to be constantly adjusted. These factors make ultrasound devices for diagnostic purposes difficult to use for monitoring during FUS procedures.
Disclosure of Invention
An object of the present invention is to provide a method of determining imaging parameters of a focused ultrasound system, a method of controlling a focused ultrasound system, an image processing apparatus, a controller, a focused ultrasound system, and a computer readable medium.
As a first aspect of the present disclosure, there is provided a method of determining imaging parameters of a focused ultrasound system, comprising:
acquiring an ultrasonic image;
identifying the position of the skin edge in the ultrasonic image;
determining the distance between the skin and the ultrasonic probe according to the position of the skin edge in the ultrasonic image;
and determining the current imaging parameters of the focused ultrasound system according to the distance between the skin and the ultrasound probe.
Optionally, the imaging parameters of the focused ultrasound system include a probe power of an ultrasound probe, and in the step of generating the current imaging parameters of the focused ultrasound system according to the distance between the skin and the ultrasound probe, the probe power is calculated according to the following formula:
P1＝k0*S1+kw*Sw；
S1＝S-Sw＝1/2*θ*(h*h-skin_dis*skin_dis)；
Sw＝1/2*θ*(skin_dis)*(skin_dis)；
wherein the content of the first and second substances,
p2 is the probe power;
s1 is the area of the organism penetrated by the ultrasonic wave in the ultrasonic image;
sw is the area of the ultrasonic wave in the ultrasonic image passing through the medium;
theta is the fan angle of the ultrasonic image;
skin _ dis is the distance between the ultrasound probe and the skin;
k0 is the average acoustic impedance coefficient of the organism;
kw is the acoustic impedance coefficient of the medium between the probe and the skin.
Optionally, the imaging parameters of the focused ultrasound system include a position of an imaging focus of the ultrasound probe, and in the step of generating current imaging parameters of the focused ultrasound system according to the distance between the skin and the ultrasound probe, the distance between the imaging focus and the ultrasound probe is calculated according to the following formula:
F＝(h+skin_dis)/2；
wherein h is the detection depth of the ultrasonic probe;
skin _ dis is the distance between the ultrasound probe and the skin.
As a second aspect of the present disclosure, there is provided a control method of a focused ultrasound system, including:
receiving current imaging parameters of the focused ultrasound system determined according to a method of one aspect of the present disclosure;
generating an adjustment signal according to a predetermined strategy and the imaging parameters;
providing the adjustment signal to a functional component of the focused ultrasound system.
Optionally, when the imaging focus of the ultrasound probe is located outside the living organism, the adjustment signal generated according to the imaging parameter comprises an adjustment signal such that the imaging focus of the ultrasound probe is located inside the living organism.
Optionally, in the step of generating an adjustment signal according to a predetermined strategy and the imaging parameters, the adjusting the time gain compensation parameter includes:
and adjusting the time gain compensation parameter to a lowest value.
As a third aspect of the present disclosure, there is provided an image processing apparatus comprising:
a first storage module having a first executable program stored thereon;
one or more first processors capable of implementing the method of the first aspect of the disclosure when the one or more first processors invoke the first executable program.
As a fourth aspect of the present disclosure, there is provided a controller comprising:
a second storage module having a second executable program stored thereon;
one or more second processors capable of implementing the control method provided by the second aspect of the present disclosure when the one or more second processors call the second executable program.
As a fifth aspect of the present disclosure, there is provided a focused ultrasound system comprising:
the image processing apparatus provided by the third aspect;
the controller provided in the fourth aspect;
and a functional component.
Optionally, the focused ultrasound system may further include an information transmission interface and an image transmission interface, the information transmission interface is disposed in the image processing apparatus to transmit the imaging parameters determined by the image processing apparatus to the controller, and the image transmission interface is configured to receive an ultrasound image.
As a sixth aspect of the present disclosure, there is provided a computer-readable medium having stored thereon an executable program capable of implementing the above-mentioned method provided by the present disclosure when the executable program is called.
The imaging parameters are mostly related to the distance between the ultrasound probe and the skin. By identifying the position of the skin in the ultrasound influence, the distance between the skin and the ultrasound probe can be determined. After the distance between the skin and the ultrasonic probe is determined, the current imaging parameters of the focused ultrasound system can be determined.
Determining the imaging parameters is equivalent to monitoring the FUS procedure. The imaging parameters may be adjusted according to FUS operating requirements.
In the present disclosure, monitoring of the FUS process can be achieved by identifying the ultrasound image without the need for human observation by the operator.
The method provided by the present disclosure may be performed by an electronic device without modification to existing ultrasound devices on the market. That is, the method provided by the present disclosure can realize the monitoring of imaging parameters in the FUS process with lower cost.
Drawings
The accompanying drawings, which are included to provide a further understanding of the invention and are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and together with the description serve to explain the principles of the invention and not to limit the invention. In the drawings:
fig. 1 is a flow chart of a method provided by a first aspect of the present disclosure;
fig. 2 is a flow chart of a method provided by a second aspect of the disclosure.
Detailed Description
In order to make the technical solutions of the present disclosure better understood, the method for determining imaging parameters of a focused ultrasound system, the control method of the focused ultrasound system, the image processing apparatus, the controller, the focused ultrasound system, and the computer readable medium provided in the present disclosure are described in detail below with reference to the accompanying drawings.
Example embodiments will be described more fully hereinafter with reference to the accompanying drawings, but which may be embodied in different forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the disclosure to those skilled in the art.
Embodiments of the present disclosure and features of embodiments may be combined with each other without conflict.
As used herein, the term "and/or" includes any and all combinations of one or more of the associated listed items.
The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the disclosure. As used herein, the singular forms "a", "an" and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms "comprises" and/or "comprising," when used in this specification, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof.
Unless otherwise defined, all terms (including technical and scientific terms) used herein have the same meaning as commonly understood by one of ordinary skill in the art. It will be further understood that terms, such as those defined in commonly used dictionaries, should be interpreted as having a meaning that is consistent with their meaning in the context of the relevant art and the present disclosure, and will not be interpreted in an idealized or overly formal sense unless expressly so defined herein.
As a first aspect of the present disclosure, there is provided a method of determining imaging parameters of a focused ultrasound system, as shown in fig. 1, the method comprising:
in step S110, an ultrasound image is acquired;
in step S120, identifying a position of a skin edge in the ultrasound image;
in step S130, determining a distance between the skin and the ultrasound probe according to the position of the skin edge in the ultrasound image;
in step S140, current imaging parameters of the focused ultrasound system are determined according to the distance between the skin and the ultrasound probe.
The imaging parameters are mostly related to the distance between the ultrasound probe and the skin. By identifying the position of the skin in the ultrasound image in step S120, the distance between the skin and the ultrasound probe can be determined. After the distance between the skin and the ultrasonic probe is determined, the current imaging parameters of the focused ultrasound system can be determined.
Determining the imaging parameters is equivalent to monitoring the FUS procedure. The imaging parameters may be adjusted according to FUS operating requirements.
In the present disclosure, monitoring of the FUS process can be achieved by identifying the ultrasound image without the need for human observation by the operator.
The method provided by the present disclosure may be performed by an electronic device without modification to existing ultrasound devices on the market. That is, the method provided by the present disclosure can realize the monitoring of imaging parameters in the FUS process with lower cost.
In the FUS process, the boundary between the medium and the skin edge is very distinct, and in the present disclosure, no special limitation is made on how to identify the position of the skin in the ultrasound image. For example, an edge detection algorithm may be used to determine skin edges in the ultrasound image. For another example, the labeled sample image may be used to train the deep learning neural network model, so as to obtain a trained neural network model. And inputting the received ultrasonic image into the trained neural network model, and outputting the position information of the skin edge in the ultrasonic image.
For ultrasound images, the surface of the ultrasound probe is either at the top of the ultrasound image or at the bottom of the ultrasound image. After the position of the skin edge in the ultrasonic image is determined, the distance between the ultrasonic probe and the skin can be determined.
For a focused ultrasound system, the imaging parameters include the probe power of the ultrasound probe, and how the probe power is calculated from the distance between the skin and the ultrasound probe is described below.
Generally, the shape of the ultrasound image is a sector, and the fan angle θ and the probe depth h (corresponding to the radius of the circle on which the sector is located) are determined.
Accordingly, the area S of the ultrasound image is:
S＝1/2*θ*h*h。
at this time, the ultrasound waves need to pass all the way through the area shown in the ultrasound image, and the required ultrasound power P0 is:
P0＝k0*S；
where k0 is the average acoustic impedance coefficient of a living body (e.g., a human body) including the skin.
By the above formula, k0, i.e., k0 ═ P0/S, can be determined computationally.
When the probe is at skin distance skin _ dis, the area of the ultrasound passing through the medium (e.g., pure water) is:
Sw＝1/2*θ*(skin_dis)*(skin_dis)；
accordingly, the area of the ultrasound wave passing through the organism is:
S1＝S-Sw＝1/2*θ*(h*h-skin_dis*skin_dis)。
when the acoustic impedance coefficient of the medium is kw, the required power is:
P1＝k0*S1+kw*Sw。
that is, in the step of generating the current imaging parameters of the focused ultrasound system from the distance between the skin and the ultrasound probe, the probe power is calculated according to the following formula:
P1＝k0*S1+kw*Sw；
S1＝S-Sw＝1/2*θ*(h*h-skin_dis*skin_dis)；
Sw＝1/2*θ*(skin_dis)*(skin_dis)；
wherein the content of the first and second substances,
p2 is the probe power;
s1 is the area of the organism penetrated by the ultrasonic wave in the ultrasonic image;
sw is the area of the ultrasonic wave in the ultrasonic image passing through the medium;
theta is the fan angle of the ultrasonic image;
skin _ dis is the distance between the ultrasound probe and the skin;
k0 is the average acoustic impedance coefficient of the organism;
kw is the acoustic impedance coefficient of the medium between the probe and the skin.
The acoustic impedance coefficient of pure water is approximately 0, so the probe power can also be calculated using the following formula:
P1＝k0*S1+0*Sw＝K0*(1/2*θ*(h*h-skin_dis*skin_dis))。
the formula for calculating the power of the probe can be selected according to the precision requirement.
In the present disclosure, k0 may be determined by a base power calculation, and kw may be determined experimentally. Of course, k0, kw may differ for different ultrasound devices or ultrasound probes.
For a phased ultrasound probe, the imaging parameters of the focused ultrasound system include, in addition to the probe power, the position of the imaging focus of the ultrasound probe, and in the step of generating the current imaging parameters of the focused ultrasound system from the distance between the skin and the ultrasound probe, the distance between the imaging focus and the ultrasound probe is calculated according to the following formula:
F＝(h+skin_dis)/2；
wherein h is the detection depth of the ultrasonic probe;
skin _ dis is the distance between the ultrasound probe and the skin.
When F < sin _ dis is calculated, the imaging focus is outside the organism, and needs to be adjusted.
As a second aspect of the present disclosure, there is provided a control method of a focused ultrasound system, as shown in fig. 2, the control method may include:
in step S210, receiving current imaging parameters of the focused ultrasound system determined according to the method provided by the first aspect of the present disclosure;
in step S220, generating an adjustment signal according to a predetermined strategy and the imaging parameters;
in step S230, the adjustment signal is provided to a functional component of the focused ultrasound system.
In the case where imaging parameters have been determined, a signal may be generated that adjusts the current imaging parameters according to a predetermined strategy. After the adjustment signal is provided to the functional component of the focused ultrasound system, the functional component can be adjusted to ensure the smooth operation of FUS.
As described hereinbefore, the adjustment signal that may be generated in accordance with the imaging parameter when the imaging focus of the ultrasound probe is located outside the living organism includes an adjustment signal that causes the imaging focus of the ultrasound probe to be located inside the living organism.
In order to reduce noise on the ultrasound image and highlight biological tissue on the ultrasound image, the Time Gain compensation parameter (TGC) may be adjusted to a minimum value after the skin edge is located, i.e. in the step of generating an adjustment signal according to the imaging parameter, adjusting the Time Gain compensation parameter comprises:
and adjusting the time gain compensation parameter to a lowest value.
In the period, the TGC parameter is the lowest, which not only can reduce noise, but also can ensure that the medium water is displayed as pure black on the final ultrasonic image, improve the imaging weight of the biological tissue and facilitate the identification of the biological tissue.
As a third aspect of the present disclosure, there is provided an image processing apparatus comprising:
a first storage module having a first executable program stored thereon;
one or more first processors capable of implementing the method provided by the first aspect of the disclosure when the one or more first processors invoke the first executable program.
Optionally, the image processing apparatus may further include a first I/O interface, connected between the first processor and the first storage module, configured to implement information interaction between the first processor and the first storage module.
Wherein, the first processor is a device with data processing capability, which includes but is not limited to a Central Processing Unit (CPU) and the like; the first storage module is a device with data storage capability, which includes but is not limited to random access memory (RAM, more specifically SDRAM, DDR, etc.), Read Only Memory (ROM), Electrically Erasable Programmable Read Only Memory (EEPROM), FLASH memory (FLASH); the first I/O interface (read/write interface) is connected between the first processor and the first memory module, and can implement information interaction between the first processor and the first memory module, which includes but is not limited to a data Bus (Bus) and the like.
In some embodiments, the first processor, the first memory module, and the first I/O interface are interconnected via a bus to further connect with other components of the computing device.
As a fourth aspect of the present disclosure, there is provided a controller comprising:
a second storage module having a second executable program stored thereon;
one or more second processors capable of implementing the control method provided by the second aspect of the present disclosure when the one or more second processors call the second executable program.
Optionally, the controller may further include a second I/O interface, connected between the second processor and the first storage module, configured to implement information interaction between the second processor and the second storage module.
Wherein the second processor is a device with data processing capability, including but not limited to a Central Processing Unit (CPU) or the like; the second storage module is a device with data storage capability, which includes but is not limited to random access memory (RAM, more specifically SDRAM, DDR, etc.), Read Only Memory (ROM), Electrically Erasable Programmable Read Only Memory (EEPROM), FLASH memory (FLASH); the second I/O interface (read/write interface) is connected between the second processor and the second memory module, and can implement information interaction between the second processor and the second memory module, which includes but is not limited to a data Bus (Bus) and the like.
In some embodiments, the second processor, the second memory module, and the second I/O interface are interconnected via a bus to further connect with other components of the computing device.
As a fifth aspect of the present disclosure, there is provided a focused ultrasound system comprising:
an image processing apparatus provided in a third aspect of the present disclosure;
the controller provided in the fourth aspect of the present disclosure;
and a functional component.
As indicated above, the functional component may be an ultrasound probe.
Optionally, the focused ultrasound system may further include an information transmission interface and an image transmission interface, the information transmission interface is disposed in the image processing apparatus to transmit the imaging parameters determined by the image processing apparatus to the controller, and the image transmission interface is configured to receive an ultrasound image.
Optionally, the video transmission interface has a function of transmitting standard signals (e.g., vga/dvi/hdmi/sdi), and can also transmit a 16-bit dicom video in real time. Alternatively, the image transmission interface may also transmit an imaging rfid signal.
In the present disclosure, the functional components of the focused ultrasound system may include, but are not limited to, an ultrasound probe, an imaging device, etc., and a plurality of functional components may constitute an ultrasound apparatus (e.g., a B-ultrasonic machine), etc.
As a sixth aspect of the present disclosure, there is provided a computer-readable medium having stored thereon an executable program capable of implementing the method provided by one or the second aspect of the present disclosure when the executable program is called.
It will be understood by those of ordinary skill in the art that all or some of the steps of the methods, systems, functional modules/units in the devices disclosed above may be implemented as software, firmware, hardware, and suitable combinations thereof. In a hardware implementation, the division between functional modules/units mentioned in the above description does not necessarily correspond to the division of physical components; for example, one physical component may have multiple functions, or one function or step may be performed by several physical components in cooperation. Some or all of the physical components may be implemented as software executed by a processor, such as a central processing unit, digital signal processor, or microprocessor, or as hardware, or as an integrated circuit, such as an application specific integrated circuit. Such software may be distributed on computer readable media, which may include computer storage media (or non-transitory media) and communication media (or transitory media). The term computer storage media includes volatile and nonvolatile, removable and non-removable media implemented in any method or technology for storage of information such as computer readable instructions, data structures, program modules or other data, as is well known to those of ordinary skill in the art. Computer storage media includes, but is not limited to, RAM, ROM, EEPROM, flash memory or other memory technology, CD-ROM, Digital Versatile Disks (DVD) or other optical disk storage, magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices, or any other medium which can be used to store the desired information and which can be accessed by a computer. In addition, communication media typically embodies computer readable instructions, data structures, program modules or other data in a modulated data signal such as a carrier wave or other transport mechanism and includes any information delivery media as known to those skilled in the art.
Example embodiments have been disclosed herein, and although specific terms are employed, they are used and should be interpreted in a generic and descriptive sense only and not for purposes of limitation. In some instances, features, characteristics and/or elements described in connection with a particular embodiment may be used alone or in combination with features, characteristics and/or elements described in connection with other embodiments, unless expressly stated otherwise, as would be apparent to one skilled in the art. Accordingly, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the scope of the disclosure as set forth in the appended claims.
Claims (11)
1. A method of determining imaging parameters of a focused ultrasound system, comprising:
acquiring an ultrasonic image;
identifying the position of the skin edge in the ultrasonic image;
determining the distance between the skin and the ultrasonic probe according to the position of the skin edge in the ultrasonic image;
and determining the current imaging parameters of the focused ultrasound system according to the distance between the skin and the ultrasound probe.
2. The method of claim 1, wherein the imaging parameters of the focused ultrasound system comprise a probe power of an ultrasound probe, the probe power being calculated in the step of generating current imaging parameters of the focused ultrasound system as a function of a distance between skin and the ultrasound probe according to the following formula:
P1＝k0*S1+kw*Sw；
S1＝S-Sw＝1/2*θ*(h*h-skin_dis*skin_dis)；
Sw＝1/2*θ*(skin_dis)*(skin_dis)；
wherein the content of the first and second substances,
p2 is the probe power;
s1 is the area of the organism penetrated by the ultrasonic wave in the ultrasonic image;
sw is the area of the ultrasonic wave in the ultrasonic image passing through the medium;
theta is the fan angle of the ultrasonic image;
skin _ dis is the distance between the ultrasound probe and the skin;
k0 is the average acoustic impedance coefficient of the organism;
kw is the acoustic impedance coefficient of the medium between the probe and the skin.
3. The method of claim 2, wherein the imaging parameters of the focused ultrasound system comprise a position of an imaging focus of the ultrasound probe, and in the step of generating current imaging parameters of the focused ultrasound system from a distance between skin and ultrasound probe, the distance between the imaging focus and ultrasound probe is calculated according to the following formula:
F＝(h+skin_dis)/2；
wherein h is the detection depth of the ultrasonic probe;
skin _ dis is the distance between the ultrasound probe and the skin.
4. A method of controlling a focused ultrasound system, comprising:
receiving current imaging parameters of the focused ultrasound system determined according to the method of any one of claims 1 to 3;
generating an adjustment signal according to a predetermined strategy and the imaging parameters;
providing the adjustment signal to a functional component of the focused ultrasound system.
5. The control method according to claim 4, wherein, when the imaging focus of the ultrasound probe is located outside a living organism, the adjustment signal generated in accordance with the imaging parameter includes an adjustment signal that causes the imaging focus of the ultrasound probe to be located inside the living organism.
6. The control method of claim 4 or 5, wherein in the step of generating an adjustment signal according to a predetermined strategy and the imaging parameters, adjusting a time gain compensation parameter comprises:
and adjusting the time gain compensation parameter to a lowest value.
7. An image processing apparatus comprising:
a first storage module having a first executable program stored thereon;
one or more first processors capable of implementing the method of any one of claims 1 to 3 when said one or more first processors invoke said first executable program.
8. A controller, comprising:
a second storage module having a second executable program stored thereon;
one or more second processors capable of implementing the control method of any one of claims 4 to 6 when said one or more second processors invoke said second executable program.
9. A focused ultrasound system, comprising:
the image processing apparatus of claim 7;
the controller of claim 8;
and a functional component.
10. The focused ultrasound system of claim 9, wherein the focused ultrasound system further comprises an information transmission interface and an image transmission interface, the information transmission interface is disposed in the image processing device to transmit the imaging parameters determined by the image processing device to the controller, and the image transmission interface is configured to receive an ultrasound image.
11. A computer readable medium having stored thereon an executable program which, when invoked, is capable of implementing the method of any one of claims 1 to 6.
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