KR20230041414A - Diagnostic probe and medical ultrasound scanner using same - Google Patents

Abstract

Disclosed are a diagnostic probe and a medical ultrasound scanner using the same. In the present invention, the ultrasound scanner for generating an ultrasound image of the inside of a skull may include: a diagnostic probe including a plurality of ultrasonic transducers, wherein at least a part of which is inserted into the skull; and a computing device receiving data measured by the diagnostic probe.

Description

Diagnostic probe and medical ultrasound scanner using the same {DIAGNOSTIC PROBE AND MEDICAL ULTRASOUND SCANNER USING SAME}

The present invention relates to a diagnostic probe and a medical ultrasound scanner using the same. More specifically, it relates to a diagnostic probe that is directly inserted into the skull and capable of performing an ultrasound scan inside the skull, and a medical ultrasound scanner using the diagnostic probe.

In general, an ultrasonic system emits an ultrasonic signal to an object to be inspected by the piezoelectric effect of a transducer, which is a transducer, receives an ultrasonic signal reflected from a discontinuous surface of the object, and converts the received ultrasonic signal into an electrical signal. It is a system that inspects the internal state of an object by converting it into a video image and outputting it to a predetermined imaging device.

That is, the ultrasound diagnosis apparatus irradiates an ultrasound signal generated from a transducer of a probe from the body surface of an object toward a target part in the body, receives information of the reflected ultrasound signal (ultrasonic echo signal), and It is mainly used for medical purposes, such as observing the inside of an object, detecting foreign substances, and measuring injuries, by obtaining images of soft tissue slices or blood flow in a non-invasive way. However, in the case of the skull, due to its thick thickness, ultrasound can't see inside it. This is because ultrasound cannot penetrate the skull. Accordingly, conventionally, the inside of the skull was observed using MRI or X-ray, but MRI equipment is excessively expensive, and X-ray has a problem in that adverse effects on the body due to radiation are concerned.

Accordingly, there is an increasing need for a technique for observing the inside of the skull using ultrasound, which is inexpensive and does not affect the body.

In addition, conventionally, a phased array ultrasound test (PAUT) method was used to generate an ultrasound image, but at least 64 piezoelectric elements are required to use it. As the number of piezoelectric elements increases, the thickness of the wire cable increases, so it cannot be inserted into the inside of the skull or blood vessels.

Republic of Korea Patent Registration No. 10-2285007 (Title of Invention: Ultrasonic Image Provisioning Apparatus and Method Using Position and Posture Tracking of Transducer of Ultrasound Scanner)

An object of the present invention is to provide a diagnostic probe that can be directly inserted through the sagittal bone inside the skull and a medical ultrasound scanner using the diagnostic probe.

Another object of the present invention is to provide a diagnostic probe in which the number of ultrasonic transducers is significantly reduced through a plurality of ultrasonic transducers rotating inside a diagnostic probe unit, and a medical ultrasound scanner using the diagnostic probe.

In order to solve the above problems, the present invention is an ultrasound scanner for generating an ultrasound image of the inside of the skull, including a plurality of ultrasound transducers, at least a part of which is inserted into the skull, and a diagnostic probe from the diagnostic probe It may include a computing device that receives the measured data.

In addition, at least a portion of the diagnostic probe may be inserted into the skull through a nostril and a through hole connected to the nostril and formed in a sagittal bone of the skull.

The diagnostic probe may further include an insertion part inserted into the skull through the nostril and the through hole, and a handle part extending to one side of the insertion part and connected to the computing device.

In addition, the plurality of ultrasound transducers are located inside the end of the diagnostic probe and inserted into the skull, radiate ultrasound signals from the inside of the skull, and receive the ultrasound signals reflected by a target inside the skull. can do.

Also, the computing device may generate an ultrasound image based on the ultrasound signals received from the plurality of ultrasound transducers.

Also, the computing device may extract a tumor image from the ultrasound image by performing a vision recognition algorithm on the ultrasound image.

In addition, in order to solve the above-described problems, the present invention is a diagnostic probe for a medical ultrasound scanner, an insertion portion inserted into the skull through the nostril and the through hole, and a handle extending to one side of the insertion portion and connected to an external device The insertion part may be inserted into the skull through a nostril and a through hole connected to the nostril and formed in a bow bone of the skull.

In addition? h, the insertion unit is located inside the end of the diagnostic probe and is inserted into the skull, radiates an ultrasonic signal from the inside of the skull, and receives the ultrasonic signal reflected by a target inside the skull. An ultrasonic transducer may be included.

According to the present invention, an ultrasound image of the inside of the skull can be obtained by emitting an ultrasound signal from the inside of the skull, so that a brain tumor can be detected at a lower cost than MRI.

In addition, the present invention has an effect of detecting brain tumors only with ultrasound, which is less harmful to the body than X-rays.

In addition, the present invention has an effect of providing a method for calculating more accurate position coordinate values by preventing an error in calculating a distance according to an ultrasonic signal in advance by going through a separate verification process.

The effects obtainable according to the present invention are not limited to the effects mentioned above, and other effects not mentioned are clearly understood by those skilled in the art from the outer surface of the protection unit below. It could be.

1 schematically shows a medical ultrasound scanner according to the present invention.
2 is a simplified representation of a computing device in accordance with the present invention.
3 shows a diagnostic probe according to the present invention.
4 shows that the diagnostic probe according to the present invention is inserted into the inside of the skull.
5 shows a sagittal bone into which a diagnostic probe according to the present invention is inserted.
6 shows a diagnostic probe according to the present invention.
7 and 8 show a plurality of ultrasonic transducers according to the present invention.
Figure 9 is a simplified representation of the functional configurations stored in the memory in accordance with the present invention.
10 shows signal detection in the signal detection module according to the present invention.
11 is a diagram showing a correlation between a first ultrasonic transducer and a second ultrasonic transducer according to the present invention.
12 is a diagram showing a graph of ultrasound measurement by three ultrasound transducers T1, T2, and T3 according to the present invention.
13 is a graph for explaining an example of verification of a learning and verification module according to the present invention.
14 shows polar coordinates derived by the position measurement module according to the present invention.
15 illustrates a display device according to the present invention and an ultrasound image displayed thereon.
16 is a diagram showing an example of an image correction filter according to the present invention.
The accompanying drawings, which are included as part of the detailed description to aid understanding of the present specification, provide examples of the present specification and describe technical features of the present specification together with the detailed description.

Hereinafter, the embodiments disclosed in this specification will be described in detail with reference to the accompanying drawings, but the same or similar elements are given the same reference numerals regardless of reference numerals, and redundant description thereof will be omitted.

In addition, in describing the embodiments disclosed in this specification, if it is determined that a detailed description of a related known technology may obscure the gist of the embodiment disclosed in this specification, the detailed description thereof will be omitted.

In addition, the accompanying drawings are only for easy understanding of the embodiments disclosed in this specification, the technical idea disclosed in this specification is not limited by the accompanying drawings, and all changes included in the spirit and technical scope of the present invention , it should be understood to include equivalents or substitutes.

Terms including ordinal numbers, such as first and second, may be used to describe various components, but the components are not limited by the terms. These terms are only used for the purpose of distinguishing one component from another.

Singular expressions include plural expressions unless the context clearly dictates otherwise.

In this application, terms such as "comprise" or "having" are intended to designate that there is a feature, number, step, operation, component, part, or combination thereof external to the protection unit in the specification, but one or It should be understood that it does not preclude the possibility of the presence or addition of other features, numbers, steps, operations, components, parts, or combinations thereof beyond that.

Hereinafter, a diagnostic probe and a medical ultrasound scanner using the diagnostic probe according to a preferred embodiment of the present specification will be described in detail based on the above information.

1 schematically shows a medical ultrasound scanner according to the present invention.

According to FIG. 1 , a medical ultrasound scanner according to the present invention may include a diagnostic probe 100 and a computing device 200 . The diagnostic probe 100 according to the present invention includes a plurality of ultrasonic transducers 110, and at least some of them may be inserted into the skull.

That is, the diagnostic probe 100 according to the present invention may be inserted into the skull to emit an ultrasonic signal, and receive the emitted and reflected ultrasonic signal again.

In addition, the computing device 200 according to the present invention is connected to the diagnostic probe 100 wired/wireless, and may calculate or convert data received from the diagnostic probe 100 into image data. In addition, the computing device 200 according to the present invention may further include a display device (not shown).

At least a part of the diagnostic probe 100 of the present invention may be inserted into the inside of the skull through a through hole (311 in FIG. 5) formed in the nostril and the scapula (310 in FIG. 5). In this case, the through hole (311 in FIG. 5) formed in the sagittal bone (310 in FIG. 5) may be connected to the nostril.

2 is a simplified representation of a computing device in accordance with the present invention.

According to FIG. 2 , a computing device 200 according to the present invention may include a processor 210, a memory 220, and a communication module 230.

The processor 210 according to the present invention may control components of the computing device 200 . The processor 210 may execute instructions stored in the memory 220 . Commands stored in the memory 220 may be previously stored as commands for controlling other configurations.

The processor 210 is a component capable of performing calculations and controlling other devices. Mainly, it may mean a central processing unit (CPU), an application processor (AP), a graphics processing unit (GPU), and the like. Also, the CPU, AP, or GPU may include one or more cores therein, and the CPU, AP, or GPU may operate using an operating voltage and a clock signal. However, while a CPU or AP consists of a few cores optimized for serial processing, a GPU may consist of thousands of smaller and more efficient cores designed for parallel processing.

The processor 210 may provide or process appropriate information or functions to a user by processing signals, data, information, etc. input or output through the components described above or by running an application program stored in the memory 220.

The memory 220 stores data supporting various functions of the computing device 200 . The memory 220 may store a plurality of application programs (or applications) running in the computing device 200 , data for operating the computing device 200 , and instructions. At least some of these application programs may be downloaded from the external server 40 through wireless communication. Also, the application program may be stored in the memory 220, installed in the computing device 200, and driven by the processor 210 to perform an operation (or function) of the computing device 200.

The memory 220 may be a flash memory type, a hard disk type, a solid state disk type, a silicon disk drive type, or a multimedia card micro type. ), card-type memory (eg SD or XD memory, etc.), RAM (random access memory; RAM), SRAM (static random access memory), ROM (read-only memory; ROM), EEPROM (electrically erasable programmable read -only memory), a programmable read-only memory (PROM), a magnetic memory, a magnetic disk, and an optical disk. Also, the memory 220 may include a web storage performing a storage function on the Internet.

The communication module 230 may be a component for communicating between the computing device 200 and an external device or external server. In the case of the communication module 230, transmission and reception of information with a base station or a server 30 including a communication function is performed through an antenna. The communication module 230 may include a modulation unit, a demodulation unit, a signal processing unit, and the like.

Wireless communication may refer to communication using a wireless communication network using a communication facility previously installed by telecommunication companies and a frequency of the communication facility. At this time, the communication module 230 is CDMA (code division multiple access), FDMA (frequency division multiple access), TDMA (time division multiple access), OFDMA (orthogonal frequency division multiple access), SC-FDMA (single carrier frequency division multiple access), and the like, as well as the communication module 230 can also be used for 3rd generation partnership project (3GPP) long term evolution (LTE). In addition, not only 5G communication currently commercialized, but also 6G communication scheduled for commercialization in the future may be used. However, the present specification may utilize a pre-installed communication network without being bound by such a wireless communication method.

The computing device 200 according to FIG. 2 may further include a display device 240 . The display device 240 according to the present invention may refer to a device that receives screen data from the processor 210 and displays it so that the user can check it through senses. The display device 240 may include a self-emissive display panel or a non-emissive display panel. For example, an OLED panel that does not require a backlight may be exemplified as a self-emissive display panel, and an LCD panel that requires a backlight may be exemplified as a non-emissive display panel, but is not limited thereto.

3 shows a diagnostic probe according to the present invention.

According to FIG. 3 , the diagnostic probe 100 according to the present invention may include an insertion part 130 and a handle part 140 . In addition, the diagnostic probe 100 according to the present invention may include an end 120 positioned at one end of the insertion part 130 and an ultrasonic transducer 110 positioned inside the end 120 .

The insertion part 130 according to the present invention may be inserted into the skull through the nostrils and through the navicular holes. Since the insertion part 130 according to the present invention needs to undergo a sterilization or washing process to be inserted into the body, it may be made of a material having a physically and chemically strong and stable structure.

The handle part 140 according to the present invention may refer to a part that a user holds by hand to directly insert the diagnostic probe 100 into the patient's skull. The handle part 140 according to the present invention is formed to extend to one side of the insertion part 130, and can be connected to a computing device (200 in FIGS. 1 and 2, hereinafter the same) in the opposite direction of the insertion part 130. . Specifically, the handle portion 140 may include a wire connected to the ultrasonic transducer 110 therein, and the wire connected to the ultrasonic transducer 110 may be electrically connected to the computing device 200 . In addition, the handle part 140 may have a built-in communication chip (not shown) to transmit/receive data wirelessly with the computing device 200 without a wire.

The ultrasonic transducer 110 according to the present invention may include an ultrasonic generating module (not shown) for generating ultrasonic waves and an ultrasonic receiving module (not shown) for detecting ultrasonic waves. That is, the ultrasonic transducer 110 according to the present invention may refer to a device capable of converting electrical signals into ultrasonic waves and converting ultrasonic waves into electrical signals. In addition, the ultrasonic transducer 110 according to the present invention may be a plurality of transducers.

The end 120 according to the present invention includes the ultrasonic transducer 110 therein, and may be configured to separate the ultrasonic transducer 110 from liquid inside the skull. An empty space for accommodating the ultrasonic transducer 110 is formed inside the end 120, and the end 120 may not include any metal components so that ultrasonic signals can be easily transmitted and received.

The computing device 200 according to the present invention may receive an electrical signal generated from the ultrasonic transducer 110 installed inside the end 120 and store or learn it.

4 shows the diagnostic probe according to the present invention inserted into the inside of the skull, and FIG. 5 shows the sacroiliac bone into which the diagnostic probe according to the present invention is inserted.

According to FIG. 4 , the diagnostic probe 100 according to the present invention may be inserted into the skull 300 through the nostril 320 . Specifically, the diagnostic probe 100 according to the present invention may be inserted into the skull 300 through a through hole (311 in FIG. 5 ) located in the nostril 320 and the scapula 310 . The diagnostic probe 100 according to the present invention may be inserted through a through hole (311 in FIG. 5) located in the nostril 320 and the scapula 310 to an area where the pituitary gland is located in the center of the skull 300. When the diagnostic probe 100 according to the present invention is located in the center of the skull 300, the ultrasonic transducer 110 located inside the end (120 in FIG. 2) of the diagnostic probe 100 transmits ultrasound into the skull 300. signal can be emitted.

That is, the ultrasonic transducer 110 according to the present invention is located inside the end (120 in FIG. 2) of the diagnostic probe 100, is inserted into the skull 300, and emits an ultrasonic signal from the inside of the skull 300. And, it may be to receive the ultrasonic signal reflected on the target inside the skull 300. In this case, the target may mean a defect area inside the skull. That is, the target may mean a tumor generated inside the skull (or brain).

According to FIG. 5 , the scapula 310 may include two through holes 311 in the center. At this time, the fossa pterygoidea 311 included in the sagittal bone 310 may pass through and be connected to the two nostrils 320 respectively. The through hole 311 is a position where a cotton swab is inserted during a recent COVID-19 virus test.

6 shows a diagnostic probe according to the present invention, and FIGS. 7 and 8 show a plurality of ultrasonic transducers according to the present invention.

According to FIG. 6 , a plurality of ultrasonic transducers 110 may rotate while being connected to a rotation motor. The rotary motor may convert electrical energy into kinetic energy and may be connected to a plurality of ultrasonic transducers 110 along a central axis.

7 is a plurality of ultrasonic transducers 110, showing 13 ultrasonic transducers 110 arranged in a circle. According to the present invention, the plurality of ultrasound transducers 110 may generate an ultrasound image of the inside of the skull using only at least 13 ultrasound transducers. The computing device 200 according to the present invention may detect the occurrence of a tumor, which is a defect inside the skull, based on data received from 13 ultrasonic transducers.

8 shows that a plurality of ultrasonic transducers 110 according to the present invention rotate about a central axis. 8 includes FIGS. 8(a) and 8(b) showing different numbers of ultrasonic transducers 110.

Conventionally, many ultrasound transducers should have been used to generate an ultrasound image, but according to the present invention, an ultrasound image without a blank area can be generated with a much smaller number of ultrasound transducers 110 by using a rotary motor.

Figure 9 briefly shows the functional components stored in the memory according to the present invention, and Figure 10 shows signal detection in the signal detection module according to the present invention.

According to FIG. 9 , the memory 220 according to the present invention may include a signal detection module 221, a location measurement module 222, and a learning and verification module 223.

The signal detection module 221 according to the present invention extracts an ultrasonic peak based on the change in amplitude of the ultrasonic signals detected by the ultrasonic transducer (110 in FIGS. 3 and 6 to 8, hereinafter the same). can In this case, the extracted ultrasonic peak may be an ultrasonic peak having the largest amplitude.

The signal detection module 221 according to the present invention may extract one ultrasonic peak through the process according to FIG. 10 . That is, the ultrasonic transducer (110 in FIGS. 7 and 8 ) may periodically receive an ultrasonic signal reflected from the target while rotating, and measure the position of the target while rotating to measure the ultrasonic signal according to the change in distance from the target. Intensity changes may occur. That is, the distance between the ultrasonic transducer 110 and the target DF may change as the plurality of ultrasonic transducers (110 in FIGS. 7 and 8) get closer and further away from the position of the target DF while rotating. . During rotation of the plurality of ultrasonic transducers (110 in FIGS. 7 and 8 ), the intensity of the ultrasonic signal received at the point where the distance between the position of the target DF and the ultrasonic transducer 110 is the shortest is measured.

The position measurement module 222 according to the present invention may extract distance information between each ultrasonic transducer and the target DF. That is, the location measurement module 222 may extract distance information according to the time at which the ultrasonic signal is received based on previously stored information about speed, wavelength, frequency, and the like of the ultrasonic wave. In addition, the position measurement module 222 may store distance information between each ultrasonic transducer (110 in FIGS. 7 and 8).

In the position measurement module 222 according to the present invention, in order to derive distance information from the target DF, the first ultrasonic transducer (T1 in FIGS. 7 and 8) and the second ultrasonic transducer (FIG. 7 and FIG. 8) T2) of 8 is required. Therefore, the position measuring module 222 according to the present invention is based on the ultrasonic signals measured from the first ultrasonic transducer (T1 in FIGS. 7 and 8) and the second ultrasonic transducer (T2 in Figs. 7 and 8). , it is possible to derive the first location information with the target DF.

In addition, the position measuring module 222 according to the present invention is based on the ultrasonic signals measured from the first ultrasonic transducer (T1 in FIGS. 7 and 8) and the third ultrasonic transducer (T2 in Figs. 7 and 8). , second location information with the target DF can be derived.

In addition, the location measurement module 222 according to the present invention may measure the location of the defect DF using a diffraction wave timing method and/or a triangulation method.

The location measurement module 222 according to the present invention may reduce an error in distance information with the target DF based on the first location information and the second location information. Specifically, the location measurement module 222 may derive an average coordinate of coordinates according to the first location and coordinates according to the second location. Through average calculation, the present invention can correct or reduce errors in measured positional coordinates.

The learning and verification module 223 according to the present invention may predict distance information along the time axis through a linear regression model and derive erroneously derived distance information based on a difference between the predicted distance information and the derived distance information. . A description related to this will be described later with reference to FIG. 13 .

According to FIG. 9 , the memory 220 according to the present invention may further include an image generating module 224 and an image learning module 225 .

The image generation module 224 according to the present invention may generate image data including location information of the target DF based on coordinate information derived from the location measurement module 222 .

The image generation module 224 according to the present invention is based on the relative position coordinates of the ultrasonic transducers (T1, T2, T3, etc. in FIGS. 7 and 8) input in advance with respect to the origin. Image data capable of displaying the location of the target DF may be generated. This is because the location information of the target DF measured by the location measurement module 222 includes relative location information about the ultrasonic transducers (T1, T2, T3, etc. in FIGS. 7 and 8).

The position measurement module 222 according to the present invention may measure the position of the inner surface of the skull in the same way as the position of the target DF. Also, the image generating module 224 according to the present invention may generate image data including the position of the inner surface of the skull in the same manner as generating image data including the position of the target DF.

The image learning module 225 according to the present invention may learn image data generated by the image generating module 224 through a deep neural network.

The deep neural network of the present invention refers to a system or network that builds one or more layers in one or more computers and performs a decision based on a plurality of data. For example, a deep neural network can be implemented with a set of layers including a convolutional pooling layer, a locally connected layer, and a fully-connected layer. For example, the overall structure of the deep neural network may be a convolutional neural network (ie, convolutional neural network; CNN) structure in which a local access layer is followed by a convolutional pooling layer, and a fully connected layer is followed by a local access layer. In addition, the deep neural network may be formed, for example, in a recurrent neural network (RNN) structure in which nodes of each layer include edges pointing to the nodes and are connected recursively. The deep neural network may include various criterion, and a new criterion may be added through analysis of an input image. However, the structure of the deep neural network according to the embodiment of the present invention is not limited thereto, and may be formed with various structures of neural networks.

The image learning module 225 according to the present invention may be a module for learning a defect (DF) of image data generated by the image generation module 224 through vision recognition based on a deep neural network pretrained through big data. there is. The image learning module 225 may learn and classify the type of target DF displayed in the image data based on the pretrained deep neural network. In addition, the image learning module 225 may select elements other than the target DF from image data including elements other than the target DF based on the pretrained deep neural network.

In addition, the image learning module 225 according to the present invention can generate an image layer capable of displaying the learning result data on an image, merge it with the image data, and provide it to the display device (240 in FIG. 2) of the present invention. there is. Examples of this will be described in FIGS. 15 and 16 below. In addition, the image learning model 225 according to the present invention may apply an image filter for image learning, and details of the image filter will be described with reference to FIG. 16 below.

According to FIG. 10 , the computing device 200 according to the present invention may receive an electrical signal that receives ultrasonic waves from the first ultrasonic transducer (T1 in FIGS. 7 and 8 ). The computing device 200 according to the present invention may calculate the location of the target DF based on the ultrasonic signal having the strongest intensity among the received electrical signals. That is, preferably, the computing device 200 according to the present invention may measure the position of the target DF by filtering only the ultrasonic signal having the highest intensity through a filter.

According to FIG. 10, only the ultrasonic signal measurement graph of the first ultrasonic transducer (T1 in Figs. 7 and 8) is shown, but the ultrasonic signal filtering process is performed by other ultrasonic transducers (T2, T3 in Figs. 7 and 8, etc.) The same can be applied to

11 is a diagram showing a correlation between a first ultrasonic transducer and a second ultrasonic transducer according to the present invention.

According to FIG. 11, the first ultrasonic transducer T1 according to the present invention may generate a first ultrasonic signal. The first ultrasound signal may be transmitted to the second ultrasound transducer T2 through at least three paths.

The first ultrasound signal according to the present invention may be reflected on the inner surface of the skull (BS) and transmitted to the second ultrasound transducer (T2) (first path). In addition, the first ultrasound signal according to the present invention may be reflected on the target DF inside the skull and transmitted to the second ultrasound transducer T2 (second path). Also, the first ultrasound signal according to the present invention may be transmitted to the second ultrasound transducer T2 along the outer surface US of the diagnostic probe 100 (third path). The outer surface (US) of the diagnostic probe 100 and the inner surface (BS) of the skull are shown as straight lines in the drawings for convenience, but are not limited thereto.

Hereinafter, in the present invention, the ultrasonic signal along the first path may be denoted as t _B , the ultrasound signal along the second path may be denoted as t _D , and the ultrasound signal along the third path may be denoted as t _S.

Comparing the first path to the third path, since the length of the first path is the longest and the length of the third path is the shortest, if the ultrasonic signals are arranged in time order, t _S , t _D , t _B will be Therefore, preferably, the computing device 200 according to the present invention t _S , according to the time order of the ultrasonic signal received from the ultrasonic transducer t _D , t _B can be divided. Hereinafter, t _S used in the present invention, t _D , t _B may mean time information (ms) of each signal.

12 is a diagram showing a graph of ultrasound measurement by three ultrasound transducers T1, T2, and T3 according to the present invention. However, the ultrasonic signals shown in FIG. 12 may mean only filtered signals as shown in FIG. 10 .

According to FIG. 12 , the first ultrasonic transducer T1 may generate a first ultrasonic signal t _i . The first ultrasonic signal t _i may be measured by the first ultrasonic transducer T1 as soon as it is generated. Also, the first ultrasonic transducer T1 may receive the ultrasonic signal t _D1 returned after the first ultrasonic signal is reflected by the defect DF. The computing device 200 according to the present invention receives the first time information t _D2 of receiving the first ultrasonic signal from the second ultrasonic transducer T2 and the first ultrasonic signal from the third ultrasonic transducer T3. The location of the target DF may be detected based on the second time information t _D3 . At this time, a method of detecting the position of the target DF may be a triangulation method or a diffraction wave time measurement method.

In addition, the computing device 200 according to the present invention provides a time (t _B2 ) at which the first ultrasound signal is reflected from the inner surface (BS) inside the skull from the second ultrasound transducer (T2), and a diagnostic probe ( A time t _S2 at which the first ultrasonic signal is reflected from the outer surface US of 100 in FIG. 1 (hereinafter the same) may be received. According to the present invention, the computing device 200 or the image generating module ( 224 in FIG. 9 ) included in the computing device 200 determines the outer surface (US) of the diagnostic probe 100 and the inside of the skull based on t _B2 and t _S2 . Image data including a pair of first boundary surfaces of the inner surface BS may be generated.

In addition, the computing device 200 according to the present invention determines the arrival time (t _B3 ) of the first ultrasound signal reflected from the inner surface (BS) inside the skull from the third ultrasound transducer (T3), and the diagnostic probe. A time t _S3 at which the first ultrasonic signal is reflected from the outer surface US of 100 and arrives there may be received. According to the present invention, the computing device 200 or the image generation module ( 224 in FIG. 9 ) included in the computing device 200 determines the outer surface (US) of the diagnostic probe 100 and the inside of the skull based on t _B3 and t _S3 . Image data including a pair of second boundary surfaces of the inner surface BS may be generated.

In addition, the computing device 200 according to the present invention may generate an average boundary surface pair by averaging the first boundary surface pair and the second boundary surface pair, and generate image data based on the average boundary surface pair.

According to FIG. 12, the second ultrasonic transducer T2 has t B2 in _which the first ultrasonic signal is reflected from the inner surface BS inside the skull, t _D3 in which the first ultrasonic signal is reflected from the target DF, and t _S2 transmitted along the outer surface US of the diagnostic probe 100 may be received.

According to FIG. 12, the third _ultrasonic transducer T3 has t B3 in which the first ultrasonic signal is reflected from the inner surface BS inside the skull, t _D3 in which the first ultrasonic signal is reflected from the target DF, and t _S3 in which the first ultrasound signal is transmitted along the outer surface US of the diagnostic probe 100 may be received.

The computing device 200 according to the present invention extracts t _D from among the received ultrasonic signals, and three ultrasonic transducers (T1, T2, T3) and a target (DF) based on t _D1 , t _D2 and t _D3 distance can be measured. The computing device 200 according to the present invention includes a first distance between the first ultrasonic transducer T1 and the second ultrasonic transducer T2, and a distance between the first ultrasonic transducer T1 and the third ultrasonic transducer T3. The second distance may be stored in advance. In addition, the computing device 200 according to the present invention may also store in advance the velocity and wavelength of ultrasonic waves generated from the ultrasonic transducers T1, T2, and T3. The computing device 200 according to the present invention may measure the distances between the three ultrasonic transducers T1, T2, and T3 and the target DF based on previously stored data and measured _tDs .

According to FIG. 12, the first ultrasonic signal generated by the first ultrasonic transducer T1 may be generated at regular intervals. In this case, the constant period may be a predetermined period, and may be determined to have a sufficient time interval so as not to interfere with the previously generated first ultrasound signal. At this time, if the constant period is too large, the resolution of the ultrasound scan may be degraded, which may require attention.

In addition, unlike FIG. 12, an example of generating another ultrasonic signal in the other ultrasonic transducers T2 and T3 is as follows.

The second ultrasonic transducer T2 according to the present invention may generate a second ultrasonic signal, and the first ultrasonic transducer T1 may receive the second ultrasonic signal. Also, the third ultrasonic transducer T3 may receive the second ultrasonic signal. However, when the second ultrasonic transducer T2 generates the second ultrasonic signal, the first ultrasonic transducer T1 generates the first ultrasonic signal with a predetermined time difference, thereby generating the first ultrasonic signal and the second ultrasonic signal. It is possible to prevent ultrasonic signals from interfering with each other.

In addition, the third ultrasonic transducer T3 according to the present invention may generate a third ultrasonic signal, and the first ultrasonic transducer T1 may receive the third ultrasonic signal. Also, the second ultrasonic transducer T2 may receive a third ultrasonic signal. However, when the third ultrasonic transducer T3 generates the third ultrasonic signal, the first ultrasonic signal and the third ultrasonic signal are generated by leaving a predetermined time difference between the generation and the time when the first ultrasonic transducer T1 generates the first ultrasonic signal. It is possible to prevent ultrasonic signals from interfering with each other. In addition, when the third ultrasonic transducer T3 generates the third ultrasonic signal, the second ultrasonic signal and the third ultrasonic signal are generated by leaving a predetermined time difference between when the second ultrasonic transducer T2 generates the second ultrasonic signal and when the second ultrasonic signal is generated. It is possible to prevent ultrasonic signals from interfering with each other.

As such, the computing device 200 according to the present invention controls the period of the ultrasonic signals generated from the first to third ultrasonic transducers T1, T2, and T3, respectively, to prevent the ultrasonic signals from interfering with each other. can do.

13 is a graph for explaining an example of verification of a learning and verification module according to the present invention.

According to FIG. 13, a graph in which the distance between T1 and the target DF according to the rotational direction of a plurality of ultrasonic transducers is measured is disclosed. The distance information may be calculated based on a predetermined period, and the amplitude of the ultrasonic signal may be the highest when the distance between T1 and the target DF is closest.

According to FIG. 13 , distance information between a first point and a second point appears similarly. The first point is a point where the distance between T1 and the target DF is correctly indicated, and the second point is a point where the distance is incorrectly indicated due to measurement error and/or ambient noise.

As described above with reference to FIG. 10 , when distance information is calculated as the point where the amplitude of the ultrasonic signal is the largest, the distance of the second point is derived as the distance between T1 and the target DF, and distance information different from the actual distance. can be derived.

Therefore, preferably, the learning and verification module 223 according to the present invention can verify the derived distance information through the following process.

(1) Learning the tendency of distance information derived for each period using a linear regression model

(2) Verification based on the learned tendency for the derived ultrasound signal with the largest amplitude

In this case, the tendency of the distance information may be learned through a linear regression model. Specifically, as the plurality of ultrasonic transducers rotate, the ultrasonic transducers may measure the distance to the target periodically. Accordingly, the tendency of the distance information may be learned based on a 1D linear regression model, and a 1D linear equation may be generated accordingly.

In addition, the tendency of the distance information may have an opposite slope of a one-dimensional linear equation after passing the shortest distance. Therefore, when it is determined that the shortest distance has passed (when the tendency changes rapidly), a new one-dimensional linear formula can be created, and the new one-dimensional linear formula will include a slope opposite to that of the previous one-dimensional linear formula. can

In this way, if the tendency of distance information is learned, it may be possible to predict a specific point. Therefore, the learning and verification module according to the present invention can verify the point on the graph extracted as distance information from the defect DF based on the learned tendency.

For example, the second point may be extracted as distance information. The learning and verification module according to the present invention may derive a prediction point of a period corresponding to the second point in order to verify the second point. A prediction point of a period corresponding to the second point may be derived based on the learned tendency. The learning and verification module according to the present invention may calculate a distance between the predicted point and the second point on the graph, and verify the second point based on the calculated distance on the graph.

The Euclidean distance d may be one of various ways to represent the distance between two points. In this case, the distance on the graph may be calculated by Equation 1 below. Equation 1 below is a formula for obtaining a Euclidean distance.

[Equation 1]

However, X _E and X ₂ may mean coordinate information on the time-distance graph, X _E is the coordinates of the expected point derived by the tendency (x1, y1), and X ₂ is the coordinate of the second point It can be (x2, y2).

The learning and verification module according to the present invention may classify the second point as being due to an error when the Euclidean distance d(X _E , X ₂ ) calculated by Equation 1 is greater than a predetermined size. In this case, a distance value serving as a criterion for classification may be expressed as Equation 2 below.

[Equation 2]

However, α is a constant that can be determined between 0.5 and 1.5, preferably α can be 0.9 to 1.2. In addition, the first point in Equation 2 may mean not only the first point indicated in FIG. 12 but also an arbitrary point, and the third point in Equation 2 may mean not only the third point indicated in FIG. It may mean one of the points immediately adjacent to the point of .

[Experimental Example 1]

In the verification process according to the present invention, the accuracy according to the result of the defect (DF) verification according to the application range of α is as follows. The table below shows the accuracy of the verification result according to the application range of α as a numerical value, requested by a person in the relevant technical field.

accuracy (score) 81 98 84

Table 1 shows the scores for accuracy evaluated by experts for each case. This experimental example is an experiment based on 12 tumor-generating patient samples, and measures the accuracy of the information on the actual defect (DF) and the verification result on a scale of 100 points.

As can be seen in Table 1, differences in accuracy were confirmed according to the application range of α. The learning and verification module according to the present invention can perform a verification process with higher accuracy through α in the range of 0.9 or more and less than 1.1.

14 shows polar coordinates derived by the position measurement module according to the present invention.

According to FIG. 14 , the center point (origin) may refer to an end ( 120 of FIGS. 2 and 6 ) or an ultrasonic transducer inside the end ( 120 of FIGS. 2 and 6 ) of the diagnostic probe 100 . That is, the positional coordinates of the ultrasonic transducer or the average positional coordinates of the plurality of transducers may correspond to the origin polar coordinates of (0, 0, 0). In addition, the 3D polar coordinates may be expressed as a rotation angle α that rotates 360 degrees according to a cycle, a distance λ between the origin and the target DF, and a declination angle β from the reference plane.

15 illustrates a display device according to the present invention and an ultrasound image displayed thereon.

According to FIG. 15 , the medical ultrasound scanner according to the present invention may detect the position of the target DF along the rotation direction of the ultrasound transducer. The medical ultrasound scanner according to the present invention re-verifies the image data level through the image learning module, and displays the result using a bounding box as shown in FIG. 15, thereby providing more accurate and diverse information to the user. have an effect

16 is a diagram showing an example of an image correction filter according to the present invention.

According to FIG. 16, types and functions of filters are shown. That is, the CNN algorithm may be a learning algorithm using a plurality of layers. In addition, the CNN algorithm can automatically learn a filter that maximizes image classification accuracy, and by adding a new layer called a convolutional layer and a polling layer before the fully connected layer, after applying the filtering technique to the original image, the filtered image A classification operation can be performed on . The CNN algorithm is configured to apply a filtering technique to the original image by adding a new layer, called a convolutional layer and a pooling layer, before the fully-connected layer, and then perform a classification operation on the filtered image. can

At this time, the operation expression for the image filter using the CNN algorithm is as shown in Equation 3 below.

[Equation 3]

(step,

G _IJ : pixel of the i-th row, j-th column of the filtered image expressed as a matrix,

F: filter,

X: image,

F _H : height of filter (number of rows),

F _W : The width of the filter (number of columns). )

Preferably, an operation expression for an image filter using the CNN algorithm is as shown in Equation 4 below.

[Equation 4]

(step,

G _IJ : pixel of the i-th row, j-th column of the filtered image expressed as a matrix,

F': application filter

X: image,

_F'H : height of application filter (number of rows),

F' _W : The width (number of columns) of the application filter.)

Preferably, F' is an applied filter and may be a filter applied to image data in order to learn and recognize the image data on which the target DF is displayed. In particular, since the target DF can be classified according to type based on differences in shape, size, and location, an application filter for effectively recognizing the shape, size, and location may be required. In order to meet this need, the application filter F' can be calculated by Equation 5 below.

[Equation 5]

: 계수, F' : 응용 필터)(However, F: filter,

: Coefficient, F' : Application filter)

In this case, the filter according to each F may be a matrix of any one of an edge detection filter according to FIG. 15, a sharpen filter, and a box blur filter.

를 구하는 연산식은 아래의 수학식 4와 같다. 이때,

는 필터의 효율을 높이기 위하여 사용되는 하나의 변수로서 해석될 수 있으며, 그 단위는 무시될 수 있다. Preferably,

The operation expression for obtaining is as shown in Equation 4 below. At this time,

can be interpreted as a variable used to increase the efficiency of the filter, and its unit can be ignored.

[Equation 6]

However, the diameter (diameter) of the lens of the camera used to capture the image may be in mm, the ultrasonic generation period may be in ms, and t _i and t _D may respectively represent signal detection times in ms. In addition, t _i is the time (ms) for generating the first ultrasonic signal in the first ultrasonic transducer (T1), and t _D is the ultrasonic signal reflected from the coupling in the n-th ultrasonic transducer (T1, T2, T3) It may mean the detected time (ms).

[Experimental Example 2]

Regarding the image data according to the present invention, when the applied filter F' of the present invention is applied, the accuracy of information on the actual target DF is as follows. The table below shows the accuracy of the recognition result as a numerical value, depending on whether a filter is applied or not, requested by a person in the relevant technical field.

no filter applied

적용filter

apply filter

apply accuracy (score) 60 85 98

Table 2 shows the scores for accuracy evaluated by experts for each case. This experimental example was experimented on the basis of 12 patient samples, and the accuracy of the information about the actual defect (DF) and the information expressed in the image data was measured out of 100 points. Each patient sample was subjected to MRI and X-ray examination after the experiment, and the accuracy was evaluated based on the examination results. This accuracy was calculated based on the location of the actual tumor.

As can be seen in Table 2, in the case where no filter is applied, there is a probability that an element other than the target DF is recognized, and thus the evaluation is performed with relatively low accuracy. In contrast, the accuracy was slightly higher when the general CNN filter F was applied, but it was confirmed that the accuracy was remarkably improved when the applied filter F' was applied.

As described above, the contents described based on the first ultrasonic transducer T1 in the description of an embodiment of the present invention are the contents of the second ultrasonic transducer T2 and the third ultrasonic transducer T3. It can be understood by replacing with Likewise, contents described based on the first ultrasound signal may be understood as being substituted with contents about the second ultrasound signal and the third ultrasound signal.

In addition, the computing device 200 according to the present invention or components belonging to the computing device 200 may derive a result by synthesizing the results of the first ultrasound signal to the results of the third ultrasound signal. It may be inferred from the contents of the specification.

In addition, the present invention is described in terms of the first to third ultrasonic transducers, but may also be understood in the same manner as ultrasonic transducers exceeding three.

The above-described present invention can be modeled as a computer readable code on a medium on which a program is recorded. The computer-readable medium includes all types of recording devices in which data readable by a computer system is stored. Examples of computer-readable media include Hard Disk Drive (HDD), Solid State Disk (SSD), Silicon Disk Drive (SDD), ROM, RAM, CD-ROM, magnetic tape, floppy disk, optical data storage device, etc. , and also includes those modeled in the form of carrier waves (eg, transmission over the Internet). Accordingly, the above detailed description should not be construed as limiting in all respects and should be considered illustrative. The scope of this specification should be determined by reasonable interpretation of the appended claims, and all changes within the equivalent scope of this specification are included in the scope of this specification.

Any or other embodiments of the present invention described above are not mutually exclusive or distinct. Certain or other embodiments of the present invention described above may be used in combination or combination of respective configurations or functions.

The above detailed description should not be construed as limiting in all respects and should be considered illustrative. The scope of the present invention should be determined by reasonable interpretation of the appended claims, and all changes within the equivalent scope of the present invention are included in the scope of the present invention.

100: diagnostic probe
200: computing device

Claims (8)

An ultrasound scanner for generating an ultrasound image of the inside of the skull,
a diagnostic probe including a plurality of ultrasonic transducers, at least a part of which is inserted into the skull; and
A computing device for receiving the data measured by the diagnostic probe; including,
Medical ultrasound scanner.
According to claim 1,
At least some of the diagnostic probes,
It is connected to the nostril and the nostril and is inserted into the skull through a through hole formed in the bow bone of the skull,
Medical ultrasound scanner.
According to claim 2,
The diagnostic probe,
an insertion unit inserted into the skull through the nostril and the through hole; and
Further comprising a handle portion extending to one side of the insertion portion and connected to the computing device.
Medical ultrasound scanner.
According to claim 1,
The plurality of ultrasonic transducers,
Located inside the end of the diagnostic probe and inserted into the skull, emitting an ultrasonic signal from the inside of the skull, and receiving the ultrasonic signal reflected by a target inside the skull,
Medical ultrasound scanner.
According to claim 4,
The computing device,
Generating an ultrasound image based on the ultrasound signals received from the plurality of ultrasound transducers,
Medical ultrasound scanner.
According to claim 5,
The computing device,
Extracting a tumor image from the ultrasound image by performing a vision recognition algorithm on the ultrasound image;
Medical ultrasound scanner.
A diagnostic probe for a medical ultrasound scanner,
an insertion unit inserted into the skull through the nostril and the through hole; and
A handle portion extending to one side of the insertion portion and connected to an external device; including,
the insertion part,
It is connected to the nostril and the nostril and is inserted into the skull through a through hole formed in the bow bone of the skull,
Diagnostic probe for ultrasound scanners.
According to claim 7,
The insertion part,
and including a plurality of ultrasonic transducers positioned inside the end of the diagnostic probe and inserted into the skull, emitting ultrasonic signals from the inside of the skull, and receiving the ultrasonic signals reflected on a target inside the skull. person,
Diagnostic probe for ultrasound scanners.

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