KR20230166390A - System and Method for Realizing 3D Photoacoustic Macroscopy using Ultrasound Guided Breath-Compensation - Google Patents

Abstract

The present invention detects distortion of the skin surface due to breathing through ultrasonic signals and uses this to correct signal distortion due to breathing to improve photoacoustic image implementation performance. Implementation of 3D photoacoustic images using ultrasound-based respiration correction. This relates to an apparatus and method for positioning an imaging probe at the starting position of a set scanning area, alternately measuring ultrasonic signals and photoacoustic signals at each imaging position, and moving the imaging probe to the next position for all imaging areas. Photoacoustic-ultrasound imaging device that performs data acquisition; detects the skin signal using the acquired ultrasound data, corrects the distortion, calculates the difference between the corrected skin signal and the previous skin signal to calculate the correction parameter, and calculates the correction parameter. It includes a signal distortion correction unit that corrects distortion caused by breathing by applying it to 3D ultrasound and photoacoustic data.

Description

Device and method for realizing 3D photoacoustic imaging using ultrasound-based breathing compensation {System and Method for Realizing 3D Photoacoustic Macroscopy using Ultrasound Guided Breath-Compensation}

The present invention relates to photoacoustic imaging technology, and specifically, an ultrasound-based device that detects distortion of the skin surface due to respiration through ultrasonic signals and uses this to correct signal distortion due to respiration to improve photoacoustic imaging performance. This relates to an apparatus and method for implementing 3D photoacoustic images using breathing correction.

Photoacoustic imaging technology is a technology that uses the photoacoustic effect to image objects such as biological tissue.

When non-ionizing laser pulses are radiated to an object, the emitted energy is converted into heat in the object, and thermoelastic expansion generates wide-band ultrasound.

In this way, photoacoustic imaging technology collects ultrasonic waves generated from an object by a laser pulse using an ultrasonic transducer and constructs an image using the collected ultrasonic information.

In this way, photoacoustic imaging is a method of imaging by acquiring photoacoustic (optoultrasonic) signals generated by thermal expansion of tissue following absorption of light. It provides not only structural information but also functional molecular images through analysis of optical absorption of biological tissue. It is used in various preclinical and clinical biomedical research.

Photoacoustic macroscopy is an imaging method that can obtain whole-body images of small animals (mice, rats) with a resolution of tens to hundreds of ㎛, mainly by mechanically scanning a single-element ultrasound transducer.

However, the mechanical scanning required to obtain a full-body image takes tens of minutes to obtain a single image, and during this time, signal distortion in the depth direction (z-direction) occurs due to the breathing of the anesthetized rat.

Accordingly, an image representation method that cannot express 3D data as is and hides distorted signals by projecting onto the x-y plane has been mainly used. This causes the spatial information contained in the data to be lost, making 3D analysis impossible, and depth direction analysis is impossible, so information about the depth at which the signal in the 2D plane was generated is lost.

To overcome this, the data acquisition time was mainly minimized using fast scanning, but it is still impossible to create 3D images because distortion caused by breathing cannot be corrected.

Also, a correction method using photoacoustic signals minutely generated from the skin has been attempted, but it is difficult to use as a general-purpose method because photoacoustic signals are not generated in areas without light absorption. Additionally, a method to correct motion by continuously acquiring multiple images has been proposed, but it has the disadvantage of requiring additional time to obtain multiple images.

As such, the image output method of the prior art has the limitation of not utilizing all the three-dimensional data that can be obtained through photoacoustic images due to data distortion caused by the respiration of small animals and forming images by projecting them onto a two-dimensional plane.

Therefore, there is a need for the development of a new technology that corrects signal distortion caused by respiration and enables the implementation of 3D images with respiration corrected, which could not be shown in photoacoustic macroscopy of the prior art.

Republic of Korea Patent Publication No. 10-2009-0088909 Republic of Korea Patent Publication No. 10-2020-0063573 Republic of Korea Patent Publication No. 10-2015-0121872

The present invention is intended to solve the problems of the photoacoustic imaging technology of the prior art. The present invention detects distortion of the skin surface due to respiration through ultrasonic signals and uses this to correct signal distortion due to respiration to improve photoacoustic imaging performance. The purpose is to provide a device and method for realizing 3D photoacoustic images using ultrasound-based breathing correction.

The present invention uses a photoacoustic-ultrasound imaging device that alternately acquires photoacoustic signals and ultrasonic signals, detects distortion of the skin surface due to the subject's breathing through ultrasonic signals, and uses this to produce a three-dimensional image with correction for respiration. The purpose is to provide a device and method for implementing a 3D photoacoustic image using ultrasound-based respiration correction that enables mapping of 3D oxygen saturation information using multi-wavelength signals.

The present invention can obtain depth information of the photoacoustic signal by applying correction parameters to the photoacoustic data at each measurement position obtained from ultrasound data to obtain corrected 3D photoacoustic data, and can obtain depth information of the photoacoustic signal in the same depth area from the skin. The purpose is to provide a device and method for implementing 3D photoacoustic imaging using ultrasound-based respiration correction that allows analysis of the photoacoustic signal distribution of biological tissue.

The present invention renders 3D data as is through respiration correction to implement a 3D image, enabling analysis in the depth direction, and uses multi-wavelength data to obtain molecular image information including 3D oxygen saturation and its distribution. The purpose is to provide a device and method for realizing 3D photoacoustic images using ultrasound-based respiration correction that can be expressed as an image.

Other objects of the present invention are not limited to the objects mentioned above, and other objects not mentioned will be clearly understood by those skilled in the art from the description below.

In order to achieve the above object, a device for implementing a 3D photoacoustic image using ultrasound-based respiration correction according to the present invention positions an imaging probe at the starting position of a set scanning area, and transmits ultrasonic signals and photoacoustics at each image position. A photoacoustic-ultrasound imaging device that alternately measures signals and moves the imaging probe to the next position to acquire data for all image areas; detects skin signals using the acquired ultrasound data, corrects distortion, and then It is characterized in that it includes a signal distortion correction unit that calculates a correction parameter by calculating the difference between the skin signal and the previous skin signal and applies the correction parameter to 3D ultrasound and photoacoustic data to correct distortion caused by breathing.

Here, a MAP image projected onto each plane is obtained using the 3D data corrected in the signal distortion correction unit, and a data analysis unit is further included to enable 3D molecular information mapping by acquiring multi-wavelength data. .

In addition, the signal distortion correction unit calculates correction parameters, applies them to 3D ultrasound and photoacoustic data, and corrects distortion caused by breathing by moving the correction parameter in the z direction.

In addition, the photoacoustic-ultrasound imaging device has a scan area setting unit that sets the area for scanning, and positions the imaging probe at the starting position. When ultrasonic signals and photoacoustic signals are alternately measured at each image position, the next A probe movement control unit that controls the movement of the imaging probe to each position, an ultrasonic application and reception unit that applies and receives ultrasonic waves to alternately measure ultrasonic signals and photoacoustic signals at each image location, and an ultrasonic signal and photoacoustic signal at each image location. It is characterized by comprising a pulse light source irradiation and photoacoustic signal reception unit that irradiates a pulse light source and receives a photoacoustic signal in order to alternately measure signals.

In addition, the probe movement control unit measures ultrasonic signals and photoacoustic signals alternately at each image location, allowing the probe to stop after movement (Stop and Go scanning) or perform data acquisition while continuously moving (Continuous scanning). It is characterized by controlling probe movement.

In addition, the signal distortion correction unit includes a skin profile extraction and correction unit that detects the skin signal using the ultrasound data obtained when data acquisition is performed for all image areas, processes the extracted skin signal to correct the distortion, and a skin profile extraction and correction unit that corrects the distortion by processing the extracted skin signal. A correction parameter extraction unit that calculates the correction parameter by calculating the difference between the skin signal and the previous skin signal, and a 3D device that applies the correction parameter to the 3D ultrasound data and moves it by the correction parameter in the z direction to correct distortion caused by breathing. It is characterized by comprising an ultrasonic correction data output unit and a 3D photoacoustic correction data output unit that corrects distortion caused by breathing by applying the correction parameter to the 3D photoacoustic data and moving it by the correction parameter in the z direction.

In addition, skin signal detection in the skin profile extraction and correction unit is performed on B-scan images (x-z images), and is characterized by extracting a three-dimensional skin surface by collecting skin signals in each B-scan image.

A method for implementing a 3D photoacoustic image using ultrasound-based respiration correction according to the present invention to achieve another purpose is to position an image probe at the starting position of a set scanning area and generate an ultrasound signal and a photoacoustic signal at each image position. A photoacoustic-ultrasound data acquisition step in which data acquisition is performed for all image areas by measuring alternately and moving the image probe to the next position; the skin signal is detected using the acquired ultrasound data to correct distortion, and then the corrected skin A signal distortion correction step in which correction parameters are calculated by calculating the difference between the signal and the previous skin signal and applied to 3D ultrasound and photoacoustic data to correct distortion caused by breathing; Visualizing the corrected data as a 3D image Characterized in that it includes a data analysis step of analyzing.

Here, in the signal distortion correction step, correction parameters are calculated, applied to 3D ultrasound and photoacoustic data, and the distortion caused by breathing is corrected by moving the correction parameter in the z direction.

And in the photoacoustic-ultrasound data acquisition stage, in the operation of alternately measuring ultrasonic signals and photoacoustic signals at each image location, the probe is stopped after moving and measured (Stop and Go scanning), or data is acquired while continuously moving (Continuous scanning). It is characterized by controlling the probe movement so that it can be performed.

A method for implementing a 3D photoacoustic image using ultrasound-based respiration correction according to the present invention to achieve another purpose includes setting an area for performing scanning and moving the imaging probe to the starting position; at each image position In order to acquire photoacoustic-ultrasonic images by wavelength in order to acquire multi-wavelength photoacoustic signals, ultrasonic waves are applied to the measurement object to receive reflected ultrasonic signals, and a pulse light source is irradiated to the measurement object to generate heat generated by thermoelastic expansion. Receiving a photoacoustic signal; moving the imaging probe to the next measurement position, determining whether data has been acquired for all image areas, determining whether measurement has been made for all wavelengths, and obtaining ultrasound data when measurement is completed Step of correcting distortion caused by respiration by detecting skin signals using; Step of correcting distortion caused by respiration of photoacoustic data using correction information of ultrasound data; Wavelength analysis in each voxel using corrected wavelength data It is characterized by including a step of performing (spectral unmixing) to obtain each molecule information.

As described above, the apparatus and method for implementing 3D photoacoustic images using ultrasound-based respiration correction according to the present invention has the following effects.

First, the distortion of the skin surface due to respiration is detected through ultrasonic signals and used to correct the signal distortion due to respiration, thereby improving the performance of photoacoustic imaging.

Second, by using a photoacoustic-ultrasound imaging device that alternately acquires photoacoustic signals and ultrasonic signals, distortion of the skin surface due to the subject's respiration is detected through ultrasonic signals, and this is used to create a three-dimensional image with the respiration corrected. It is possible to implement and enables mapping of 3D oxygen saturation information using multi-wavelength signals.

Third, depth information of the photoacoustic signal can be obtained by applying correction parameters to the photoacoustic data at each measurement position obtained from the ultrasound data to obtain corrected 3D photoacoustic data, and can obtain the depth information of the photoacoustic signal from the skin to the same depth area. Allows analysis of tissue photoacoustic signal distribution.

Fourth, analysis in the depth direction is possible by rendering 3D data as is through respiration correction to create a 3D image, and using multi-wavelength data, molecular image information including 3D oxygen saturation is acquired and its distribution is displayed as an image. It can be expressed as

Figure 1 is a configuration diagram showing the data processing process for implementing 3D photoacoustic images using ultrasound-based respiration correction according to the present invention.
Figure 2 is a block diagram of a device for implementing 3D photoacoustic imaging using ultrasound-based respiration correction according to the present invention.
Figure 3a is a detailed configuration diagram of the photoacoustic-ultrasound imaging device.
Figure 3b is a detailed configuration diagram of the signal distortion correction unit
Figure 4 is a configuration diagram showing imaging results using ultrasound-based respiration correction of photoacoustic signals
Figure 5 is a flow chart showing the distortion correction process due to breathing of an ultrasound-based photoacoustic signal.
Figure 6 is a flow chart showing the multi-wavelength photoacoustic data analysis process using distortion correction by ultrasound-based respiration.
Figure 7 is a comparative configuration diagram of the oxygen saturation (molecular information) distribution imaging method according to the prior art and the present invention.

Hereinafter, a preferred embodiment of the device and method for implementing a 3D photoacoustic image using ultrasound-based respiration correction according to the present invention will be described in detail as follows.

The characteristics and advantages of the device and method for implementing 3D photoacoustic images using ultrasound-based respiration correction according to the present invention will become apparent through the detailed description of each embodiment below.

Figure 1 is a configuration diagram showing a data processing process for implementing a 3D photoacoustic image using ultrasound-based respiration correction according to the present invention.

The present invention is intended to extract skin surface signals using ultrasonic waves to correct data distortion and use this to correct signal distortion. Because an ultrasonic transducer is used to acquire photoacoustic image signals, simultaneous acquisition of ultrasonic signals is possible without significant changes to the system.

Additionally, because ultrasound images are implemented using ultrasound signals reflected from tissues, signals on the skin surface can be obtained regardless of light absorption. Accordingly, compared to the skin surface extraction method using photoacoustic signals in the prior art, a clear skin surface signal can be obtained and distortion due to breathing can be accurately corrected.

To this end, the present invention uses a photoacoustic-ultrasound imaging device that alternately acquires photoacoustic signals and ultrasonic signals, detects distortion of the skin surface due to the subject's breathing through ultrasonic signals, and uses this to correct respiration. It may include a configuration that implements a 3D image.

The present invention can obtain depth information of the photoacoustic signal by applying correction parameters to the photoacoustic data at each measurement position obtained from ultrasound data to obtain corrected 3D photoacoustic data, and can obtain depth information of the photoacoustic signal in the same depth area from the skin. It may include a configuration that allows analyzing the photoacoustic signal distribution of biological tissue.

The present invention renders 3D data as is through respiration correction to implement a 3D image to enable analysis in the depth direction, and uses multi-wavelength data to obtain molecular image information including 3D oxygen saturation and its distribution. It may include a configuration that allows it to be expressed as an image.

Figure 2 is a block diagram of a device for implementing 3D photoacoustic imaging using ultrasound-based respiration correction according to the present invention.

As shown in FIG. 2, the device for implementing a 3D photoacoustic image using ultrasound-based respiration compensation according to the present invention positions an image probe at the starting position of the set scanning area and generates an ultrasound signal and a photoacoustic signal at each image position. A photoacoustic-ultrasound imaging device 100 that performs data acquisition for all image areas by measuring alternately and moving the imaging probe to the next position, and detects skin signals using the acquired ultrasound data to correct distortion. A signal distortion correction unit that calculates correction parameters by calculating the difference between the corrected skin signal and the previous skin signal, applies this to 3D ultrasound and photoacoustic data, and moves it in the z direction by the correction parameter to correct distortion caused by breathing. It includes (200) and a data analysis unit 300 that obtains a MAP image projected onto each plane using the corrected 3D data and acquires multi-wavelength data to enable 3D molecular information mapping.

Here, the detailed configuration of the photoacoustic-ultrasound imaging device 100 is as follows.

Figure 3a is a detailed configuration diagram of a photoacoustic-ultrasound imaging device.

As shown in FIG. 3A, the photoacoustic-ultrasound imaging device 100 includes a scan area setting unit 31 that sets an area for scanning, positions an image probe (ultrasonic transducer) at the starting position, and sets each image. When the ultrasonic signal and the photoacoustic signal are alternately measured at each position, the probe movement control unit 32 controls the movement of the imaging probe to the next position, and the ultrasonic signal and photoacoustic signal are alternately measured at each imaging position. An ultrasonic approving and receiving unit 33 that receives ultrasonic waves. It includes a pulse light source irradiation and photoacoustic signal reception unit 34 that irradiates a pulse light source and receives photoacoustic signals in order to alternately measure ultrasonic signals and photoacoustic signals at each image location.

Here, the operation of alternately measuring ultrasonic signals and photoacoustic signals at each image location can be measured by stopping after moving the probe (Stop and Go scanning), or data acquisition while continuously moving (Continuous scanning).

The detailed configuration of the signal distortion correction unit 200 is as follows.

Figure 3b is a detailed configuration diagram of the signal distortion correction unit.

As shown in FIG. 3B, the signal distortion correction unit 200 detects a skin signal using the ultrasound data obtained when data is acquired for all image areas, and processes the extracted skin signal to correct the distortion. An extraction and correction unit 35, a correction parameter extraction unit 36 that calculates correction parameters by calculating the difference between the corrected skin signal and the previous skin signal, and apply the correction parameters to the 3D ultrasound data in the z-direction. A 3D ultrasonic correction data output unit 37 that corrects the distortion caused by respiration by moving the correction parameter by the correction parameter, and a 3D ultrasonic correction data output unit 37 that applies the correction parameter to the 3D photoacoustic data and moves it by the correction parameter in the z direction to correct the distortion due to respiration. It includes a 3D photoacoustic correction data output unit 38.

Here, skin signal detection in the skin profile extraction and correction unit 35 is performed on B-scan images (x-z images), and is achieved by collecting skin signals in each B-scan image and extracting the three-dimensional skin surface.

Figure 4 is a configuration diagram showing imaging results using ultrasound-based respiration correction of photoacoustic signals.

By using 3D data corrected through the present invention, it is possible to implement 3D photoacoustic images using 3D data that was not fully utilized before, and by acquiring multi-wavelength photoacoustic data, molecular information including oxygen saturation Information can be expressed in three dimensions.

Figure 5 is a flow chart showing the distortion correction process due to breathing of an ultrasound-based photoacoustic signal.

As shown in FIG. 5, the process of correcting distortion of an ultrasound-based photoacoustic signal by breathing according to the present invention first sets an area for scanning (S501) and moves the image probe (ultrasonic transducer) to the starting position. .(S502)

In order to alternately measure ultrasonic signals and photoacoustic signals at each image position, ultrasonic waves are applied to the measurement object to receive reflected ultrasonic signals (S503), and a pulse light source is irradiated to the measurement object to generate thermoelastic expansion. Receive a photoacoustic (optoultrasonic) signal (S504)

Next, move the imaging probe to the next measurement position (S505).

Here, such measurement can be performed by stopping after moving the probe (Stop and Go scanning), or data acquisition can be performed while continuously moving (Continuous scanning).

This process is repeated to acquire data for all image areas (S506), and the distortion caused by breathing is corrected by detecting skin signals using the acquired ultrasound data (S507).

Then, the distortion caused by breathing in the photoacoustic data is corrected using the correction information of the ultrasound data (S508).

Here, skin signal detection is performed on B-scan images (x-z images), and the 3D skin surface can be extracted by collecting skin signals in each B-scan image. The extracted skin signal is processed to correct distortion, and then the correction parameter is calculated by calculating the difference between the corrected skin signal and the existing skin signal. This is applied to 3D ultrasound and photoacoustic data to correct distortion caused by breathing by moving the correction parameter in the z direction.

Next, the corrected data is visualized and analyzed as a 3D image (S509).

MAP images projected onto each plane can be obtained using corrected 3D data, and 3D molecular information mapping is possible by acquiring multi-wavelength data.

Figure 6 is a flow chart showing the multi-wavelength photoacoustic data analysis process using distortion correction by ultrasound-based respiration.

As shown in Figure 6, the multi-wavelength photoacoustic data analysis process using distortion correction by ultrasound-based respiration first sets the area for scanning (S601) and moves the imaging probe (ultrasonic transducer) to the starting position. .(S602)

In order to obtain multi-wavelength photoacoustic signals at each image location and to acquire photoacoustic-ultrasonic images by wavelength, ultrasonic waves are applied to the measurement object to receive reflected ultrasonic signals (S603), and a pulse light source is irradiated to the measurement object. Then, the photoacoustic (optoultrasonic) signal generated by thermoelastic expansion is received (S604).

Next, move the imaging probe to the next measurement position (S605).

By repeating this process, it is determined whether data has been acquired for all image areas (S606), and whether measurements have been made for all wavelengths (S607). When the measurement is completed, the skin signal is obtained using the acquired ultrasound data. Detects and corrects distortion caused by breathing (S608)

Then, the distortion caused by breathing in the photoacoustic data is corrected using the correction information of the ultrasound data (S609).

Next, spectral unmixing is performed on each voxel using the corrected wavelength data to obtain information on each molecule (S610).

In this way, in order to acquire multi-wavelength photoacoustic signals, the operation to acquire photoacoustic-ultrasonic images for each wavelength is repeated, and distortion caused by breathing is corrected through a skin correction algorithm using the obtained ultrasonic signals.

Based on the skin position corrected for one wavelength, the data for the remaining wavelengths are corrected so that the data for all wavelengths are aligned three-dimensionally. Using the corrected wavelength data, wavelength analysis (spectral unmixing) is performed on each voxel to obtain each molecular information, and using this, molecular information including oxygen saturation can be obtained in three dimensions.

Figure 7 is a comparative configuration diagram of the oxygen saturation (molecular information) distribution imaging method according to the prior art and the present invention.

In this way, the present invention can extract the location of the skin surface of a small animal using ultrasonic signals and correct distortion due to breathing based on this. Correction parameters can be applied to the photoacoustic data at each measurement location obtained from ultrasound data to obtain corrected 3D photoacoustic data. Through this, it is possible to obtain depth information of photoacoustic signals that were previously difficult to analyze, and to analyze the distribution of photoacoustic signals in biological tissues in the same depth area from the skin.

Previously, projections such as the Maximum Intensity Projection (MAP) method, which projects the maximum signal to the x-y plane, were used to hide signals distorted in the z-direction, but through breathing correction through the present invention, 3D data is rendered as is. It becomes possible to implement 3D images, which allows analysis in the depth direction.

In addition, using multi-wavelength data, molecular image information including 3D oxygen saturation can be obtained and the distribution can be expressed as an image.

Previously, wavelength analysis was performed using MAP images projected on the x-y plane for each wavelength, so z-direction information for each pixel was missing and accurate analysis was impossible.

However, when using respiration-corrected data through the present invention, it is possible to obtain 3D molecular information distribution by performing wavelength analysis for each voxel in 3D data.

As shown in Figure 7, 3D molecular information distribution can be obtained, so it can be efficiently used in various small animal studies such as drug delivery monitoring, in vivo molecular distribution, and 3D oxygen saturation imaging.

The device and method for implementing 3D photoacoustic images using ultrasound-based respiration correction according to the present invention described above detects distortion of the skin surface due to respiration through ultrasonic signals and uses this to correct signal distortion due to respiration. This is to improve the performance of photoacoustic imaging.

As described above, it will be understood that the present invention is implemented in a modified form without departing from the essential characteristics of the present invention.

Therefore, the specified embodiments should be considered from an illustrative rather than a limiting point of view, the scope of the present invention is indicated in the claims rather than the foregoing description, and all differences within the equivalent scope are intended to be included in the present invention. It will have to be interpreted.

100. Photoacoustic-ultrasound imaging device
200. Signal distortion correction unit
300. Data Analysis Department

Claims (11)

Photoacoustic-ultrasound, which positions the imaging probe to the starting position of a set scanning area, alternately measures ultrasound and photoacoustic signals at each imaging location, and moves the imaging probe to the next location to perform data acquisition for all imaging areas. imaging device;
Using the acquired ultrasound data, the skin signal is detected and the distortion is corrected, then the difference between the corrected skin signal and the previous skin signal is calculated to calculate the correction parameter, and this is applied to the 3D ultrasound and photoacoustic data to determine respiration. A device for implementing a three-dimensional photoacoustic image using ultrasound-based respiration correction, comprising a signal distortion correction unit for correcting distortion caused by a signal. The method of claim 1, further comprising a data analysis unit that obtains a MAP image projected onto each plane using the 3D data corrected in the signal distortion correction unit and acquires multi-wavelength data to enable 3D molecular information mapping. A device for implementing 3D photoacoustic images using ultrasound-based respiration correction, characterized in that. The method of claim 1, wherein in the signal distortion correction unit,
For the implementation of 3D photoacoustic images using ultrasound-based respiration correction, which is characterized by calculating correction parameters, applying them to 3D ultrasound and photoacoustic data, and correcting distortion caused by breathing by moving the correction parameter in the z direction. Device. The photoacoustic-ultrasound imaging device of claim 1,
A scan area setting unit that sets an area for scanning,
a probe movement control unit that positions the imaging probe at the starting position and controls movement of the imaging probe to the next position when ultrasound signals and photoacoustic signals are alternately measured at each imaging position;
An ultrasonic transmitting and receiving unit that applies and receives ultrasonic waves to alternately measure ultrasonic signals and photoacoustic signals at each image location;
3D photoacoustics using ultrasound-based respiration compensation, comprising a pulse light source irradiation and photoacoustic signal receiver for alternately measuring ultrasound signals and photoacoustic signals at each image location. A device for realizing images. The method of claim 4, wherein the probe movement control unit,
In the operation of alternately measuring ultrasonic signals and photoacoustic signals at each image location, the probe movement can be controlled to stop and measure after moving the probe (Stop and Go scanning) or to perform data acquisition while continuously moving (Continuous scanning). A device for realizing 3D photoacoustic imaging using ultrasound-based breathing correction. The method of claim 1, wherein the signal distortion correction unit,
When data acquisition is performed for all image areas, a skin profile extraction and correction unit detects skin signals using the acquired ultrasound data and processes the extracted skin signals to correct distortion;
a correction parameter extraction unit that calculates a correction parameter by calculating the difference between the corrected skin signal and the previous skin signal;
A 3D ultrasound correction data output unit that corrects distortion caused by breathing by applying a correction parameter to the 3D ultrasound data and moving it by the correction parameter in the z direction;
3D photoacoustics using ultrasound-based respiration correction, comprising a 3D photoacoustic correction data output unit that corrects distortion caused by breathing by applying correction parameters to 3D photoacoustic data and moving them by the correction parameter in the z direction. A device for realizing images. The method of claim 6, wherein the skin signal detection in the skin profile extraction and correction unit is performed by:
A device for implementing 3D photoacoustic images using ultrasound-based respiration correction, which is performed on B-scan images (xz images) and extracts 3D skin surfaces by collecting skin signals from each B-scan image. . Photoacoustic-ultrasound, which positions the imaging probe to the starting position of a set scanning area, alternately measures ultrasound and photoacoustic signals at each imaging location, and moves the imaging probe to the next location to perform data acquisition for all imaging areas. data acquisition step;
Using the acquired ultrasound data, the skin signal is detected and the distortion is corrected, then the difference between the corrected skin signal and the previous skin signal is calculated to calculate the correction parameter, and this is applied to the 3D ultrasound and photoacoustic data to determine respiration. A signal distortion correction step of correcting distortion caused by;
A method for implementing a 3D photoacoustic image using ultrasound-based respiration correction, comprising a data analysis step of visualizing and analyzing the corrected data as a 3D image. The method of claim 8, wherein in the signal distortion correction step,
For the implementation of 3D photoacoustic images using ultrasound-based respiration correction, which is characterized by calculating correction parameters, applying them to 3D ultrasound and photoacoustic data, and correcting distortion caused by breathing by moving the correction parameter in the z direction. method. The method of claim 8, wherein in the photoacoustic-ultrasound data acquisition step,
In the operation of alternately measuring ultrasonic signals and photoacoustic signals at each image location, the probe movement can be controlled to stop and measure after moving the probe (Stop and Go scanning) or to perform data acquisition while moving continuously (Continuous scanning). Method for implementing 3D photoacoustic images using ultrasound-based respiration correction. Setting an area to perform scanning and moving the imaging probe to the starting position;
In order to acquire multi-wavelength photoacoustic signals at each image location, in order to acquire photoacoustic-ultrasonic images by wavelength, ultrasonic waves are applied to the measurement object to receive reflected ultrasonic signals, and a pulse light source is irradiated to the measurement object to cause thermoelastic expansion. Receiving a photoacoustic signal generated by;
Move the imaging probe to the next measurement position, determine whether data has been acquired for all image areas, determine whether measurements have been made for all wavelengths, and when measurement is completed, use the acquired ultrasound data to detect skin signals. A step to correct distortion caused by breathing;
Correcting distortion caused by respiration of photoacoustic data using correction information of ultrasound data;
A method for implementing three-dimensional photoacoustic images using ultrasound-based respiration correction, comprising the step of performing wavelength analysis (spectral unmixing) on each voxel using the corrected wavelength data to obtain each molecular information.

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