CN113729634A - Method for processing skin photo-acoustic image - Google Patents
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Abstract
The invention provides a method for processing a skin photo-acoustic image, which comprises the following steps: (1) irradiating a target object and a reference object by using multi-wavelength light pulses, wherein the target object sends out a first photoacoustic signal, and the reference object sends out a second photoacoustic signal; (2) receiving and processing a first photoacoustic signal to obtain a first photoacoustic image; receiving and processing a second photoacoustic signal to obtain a second photoacoustic image; (3) defining respective noise areas and effective areas in the first photoacoustic image and the second photoacoustic image, and reading and calculating to obtain the average intensity of photoacoustic signals in the noise areas and the effective areas; (4) and processing the average intensity of the photoacoustic signals and extracting photoacoustic quantification parameters. The invention has the beneficial effects that: and the photoacoustic imaging technology is adopted, so that nondestructive detection and evaluation of the internal state of the measured object are realized.
Description
Technical Field
The invention relates to a method for processing a skin photo-acoustic image, and belongs to the technical field of medical images.
Background
Ultrasonic imaging is widely used in medical imaging because of its advantages of non-ionizing radiation, high resolution imaging, low price, etc. However, ultrasound imaging is generally sensitive to tissue structures and blood flow with differences in acoustic impedance and is not specific to other physicochemical properties of the tissue, and thus has limited functionality. In many medical imaging applications, ultrasound imaging needs to be used in conjunction with other radiological imaging modalities such as MRI, CT, or X-ray.
Photoacoustic imaging is a medical imaging method which is newly developed in recent years and can realize imaging of physicochemical properties of a tissue. The method combines the advantages of high contrast of pure optical imaging and high penetrability of pure ultrasound, can provide high contrast and high axial resolution, provides important means for researching the structural morphology, physiological characteristics, metabolic function, pathological information and the like of biological tissues, and has wide application prospect in the fields of biomedical clinical application, body tissue structure and functional imaging.
If ultrasound and photoacoustic bimodal simultaneous detection and imaging can be achieved, both high resolution structural imaging and high resolution and high contrast imaging of tissue physicochemical properties based on structural information can be provided. In addition, the original data of the photoacoustic imaging can be further processed to extract quantitative parameters directly related to the measured indexes, so that more bases are provided for subsequent application.
Disclosure of Invention
The technical problem to be solved by the invention is as follows: the existing imaging detection method has no specificity to the physicochemical property of the detected substance and has limited functions and application.
In order to solve the above technical problem, the present invention provides a method for processing a photoacoustic image, comprising the steps of:
the method comprises the following steps: irradiating a target object and a reference object by using multi-wavelength light pulses, wherein the target object sends out a first photoacoustic signal, and the reference object sends out a second photoacoustic signal;
step two: receiving and processing a first photoacoustic signal to obtain a first photoacoustic image; receiving and processing a second photoacoustic signal to obtain a second photoacoustic image;
step three: defining respective noise areas and effective areas in the first photoacoustic image and the second photoacoustic image, and reading and calculating to obtain the average intensity of photoacoustic signals in the noise areas and the effective areas;
step four: and carrying out data processing on the average intensity of the photoacoustic signals and extracting photoacoustic quantification parameters.
In some embodiments, the target object and the reference object are selected from a set of symmetrical positions on the same irradiated object, and the target object and the reference object are irradiated simultaneously by the same multi-wavelength light pulse.
In some embodiments, the irradiated object is the skin or mucosa within which the blood vessels are distributed.
In some embodiments, the multi-wavelength light pulse is emitted by a light pulser, a pulsed LD light source, or a pulsed LED light source.
In some embodiments, the multi-wavelength light pulse includes wavelengths of 750nm and 850 nm.
In some embodiments, the multi-wavelength light pulses are emitted from a pulsed LED light source with a repetition rate of 10Hz to 4kHz and a pulse width of 5ns to 100 ns.
In some embodiments, the active area refers to: comparing the first photoacoustic image with the second photoacoustic image, one or more regions where photoacoustic signals are significantly enhanced in the first photoacoustic image, and a region of a corresponding location on the second photoacoustic image.
In some embodiments, the photoacoustic signal average intensity refers to: on the first photoacoustic image or the second photoacoustic image, the average value of the photoacoustic intensities of the plurality of effective areas.
In some embodiments, the photoacoustic quantification parameter comprises PL, which is calculated by the formula:
PL＝PAPWS/PAnormal (1)
PAPWSaverage intensity of photoacoustic signal of target object, from PAPWS＝VROL/Vnoise_ROLCalculating to obtain; wherein, VROLIs the average intensity of the photoacoustic signal of the effective area on the first photoacoustic image, Vnoise_ROLThe average intensity of the photoacoustic signals of the noise area on the first photoacoustic image;
PAnormalfor reference of the mean intensity of the photoacoustic signal of the object, from PAnormal＝VCHR/Vnoise_CHRIs calculated to obtain, wherein, VCHRIs the average intensity of the photoacoustic signal of the effective area on the second photoacoustic image, Vnoise_CHRIs the average intensity of the photoacoustic signals of the noise region on the second photoacoustic image.
In some embodiments, the photoacoustic quantification parameter further comprises PLR, the PLR varying from 0 to 100%, the PLR calculated by the formula:
PLpreis the average intensity of photoacoustic signal, PL, of the target object at the first detection time pointpostIs the average intensity of the photoacoustic signal of the target object at the second detection time point.
The invention has the beneficial effects that: by adopting the photoacoustic imaging technology and utilizing the photoacoustic specificity of the physical and chemical properties of the measured object, high-resolution structural imaging can be provided, high-resolution and high-contrast imaging of the physical and chemical properties of the internal substance of the measured object can be provided on the basis of structural information, and the nondestructive detection and the efficient evaluation of the internal state of the measured object are realized.
Drawings
FIG. 1 is a flowchart of a detection method in embodiment 1 of the present invention.
FIG. 2 is a statistical result of the PWS ratings obtained by the patients grouped by age in example 2 of the present invention.
FIG. 3 is a statistical result of PWS ratings obtained by patient type grouping in example 2 of the present invention.
FIG. 4 is a graph comparing the PLR in example 2 of the present invention with conventional visual evaluation.
Detailed Description
Unless otherwise defined, technical or scientific terms used in the claims and the specification of this patent shall have the ordinary meaning as understood by those of ordinary skill in the art to which this patent belongs.
In the description of this patent, unless otherwise indicated, "a plurality" means two or more. The word "comprising" or "having", and the like, means that the element or item appearing before "comprises" or "having" covers the element or item listed after "comprising" or "having" and its equivalent, but does not exclude other elements or items.
The invention provides a photoacoustic image processing method, which comprises the following steps:
the method comprises the following steps: and opening the photoacoustic imaging equipment to emit multi-wavelength light pulses, wherein the repetition frequency of the light pulses is 10Hz to 4kHz, and the pulse width is 5ns to 100 ns. The multiwavelength light pulse can adopt an optical pulse device, a pulse LD light source or a pulse LED light source, and preferably adopts a pulse LED light source. The multi-wavelength light pulse irradiates the target object and the reference object, the target object sends out a first photoacoustic signal, and the reference object sends out a second photoacoustic signal.
Noise in the two photoacoustic signals is difficult to avoid because of factors such as temperature and electrical properties of the instrument itself. In order to eliminate the influence caused by noise, the target object and the reference object are selected from a group of symmetrical positions on the same irradiated object, the same group of multi-wavelength light pulses are irradiated on the target object and the reference object simultaneously, the noise of the first photoacoustic signal and the noise of the second photoacoustic signal obtained in this way are close, and the noise influence can be eliminated during data processing.
This method can be used to detect vascularity in the skin, mucous membranes, and changes in certain components of the blood (e.g., chemicals such as anaerobic hemoglobin, aerobic hemoglobin, etc.). The multi-wavelength light pulse should then include the characteristic light absorption wavelengths of the two haemoglobins mentioned above: 750nm and 850 nm.
Step two: the probe of the photoacoustic imaging apparatus receives the first photoacoustic signal and the second photoacoustic signal through the couplant, respectively. The photoacoustic imaging device processes the received photoacoustic signals to obtain a photoacoustic image of a target object under the irradiation of the multi-wavelength light pulse, and the photoacoustic image is called as a first photoacoustic image; and a photoacoustic image of the reference object under the irradiation of the multi-wavelength light pulse is referred to as a second photoacoustic image.
Step three: and comparing the first photoacoustic image with the second photoacoustic image, defining a random noise area and an effective area, reading and calculating to obtain the average intensity of photoacoustic signals in the noise area and the effective area. The delineation can be visually observed by an operator, and the more advanced mode is that the delineation is automatically selected and delineated by a computer by means of artificial intelligence.
The effective region is: when the first photoacoustic image is compared with the second photoacoustic image, one or more regions where photoacoustic signals are significantly enhanced on the first photoacoustic image, and a region of a corresponding location on the second photoacoustic image.
The average intensity of the photoacoustic signal is: on the same photoacoustic image of the first photoacoustic image or the second photoacoustic image, the average value of the photoacoustic intensities of the plurality of effective areas. For example, the intensity of the photoacoustic signals of all the effective areas on the first photoacoustic image is added up and then averaged, that is, the average intensity of the photoacoustic signals in the effective area of the first photoacoustic image is obtained.
Step four: and respectively processing the average intensity of the photoacoustic signals obtained from the first photoacoustic image and the second photoacoustic image, and extracting photoacoustic quantization parameters.
And repeating the first step to the fourth step at different detection time points, and obtaining the change relation of the internal state of the target object along with time.
Example 1
At present, a method for performing noninvasive functional quantitative detection on skin and mucosal vascular diseases and the like is not available, because clinically applied detection methods such as ultrasound, scattered light imaging, ballistic light imaging and the like are only sensitive to physical structure information of tissues, but not sensitive to pathological molecular information.
The embodiment is a method for detecting blood perfusion of skin and mucosa blood vessels based on photoacoustic imaging, and is an application of the photoacoustic image processing method provided by the invention in medicine. The method can obtain the blood flow perfusion information of the skin and the mucosa blood vessels, and is used for realizing the quantitative evaluation and the dynamic monitoring of the curative effect of the skin and the mucosa blood vessel diseases. The method comprises the following steps:
the method comprises the following steps: the patient was allowed to lie flat on the test bed to fully expose the diseased area. The multi-wavelength narrow pulse light source emits light pulses to irradiate the skin to be detected, the mucosa vascular disease tissue to be detected and the normal tissue on the opposite side to generate photoacoustic signals respectively.
Mucous membranes include, but are not limited to, respiratory mucosa, gastric mucosa, and bladder mucosa. The multi-wavelength pulse light source is an optical pulse device, a pulse LD light source or a pulse LED light source and is used for emitting a plurality of pulse lights with different wavelengths. The plurality of wavelengths includes, but is not limited to, the characteristic light absorption wavelengths of chemical substances such as anaerobic hemoglobin, aerobic hemoglobin, etc., such as 750nm and 850 nm.
Step two: the probe of the photoacoustic imaging apparatus receives a photoacoustic signal through the couplant. For the target lesion area, the probe is positioned at different positions, and multiple scanning images are taken. Each scan takes about 20 seconds and imaging of the entire lesion takes about 1-3 minutes, depending on patient compliance, which is typically longer for young patients. And the photoacoustic imaging equipment processes the received photoacoustic signals to obtain photoacoustic images of the tissues to be detected under the irradiation of the multi-wavelength light pulses.
In addition to imaging each diseased region, additional imaging of the contralateral healthy region is required. Since healthy areas have similar anatomy to diseased areas, they can be used as baseline controls and as a reference when quantifying diseased area measurements. If normal tissues exist at the symmetrical side of the focus on the anatomy, the contrast is the most ideal contrast; however, for the case of lack of contralateral control, other stable control areas can be selected as the basis for subsequent sampling.
Step three: and (3) defining random noise areas and effective areas of the photoacoustic images of the vascular disease tissues and the contralateral normal tissues in the photoacoustic images. In order to maximize the position stability of the scanned image at different time points during the imaging process, permanent skin markers (such as a special mark pen) are used to mark the scanned position on the skin surface. Then, the average intensity of the photoacoustic signals in the noise region and the effective region is read and calculated.
The effective areas are a plurality of areas on the photoacoustic image of the diseased tissue, in which the photoacoustic signal is significantly enhanced compared with the photoacoustic image of the normal tissue on the opposite side, and a plurality of areas on the photoacoustic image of the normal tissue on the opposite side at positions corresponding thereto. The average intensity of the photoacoustic signal is an average value of the photoacoustic intensities of a plurality of effective areas of the diseased tissue and the normal tissue.
Step four: and processing the average intensity of the photoacoustic signals, extracting photoacoustic quantitative parameters, obtaining the blood perfusion of vascular disease tissues at different treatment stages and the change of the blood perfusion along with time, and realizing the quantitative evaluation and dynamic monitoring of curative effect of the vascular diseases of the skin and the mucosa.
The photoacoustic signal average intensity quantization parameter includes PL and PLR. PL is the density of hemoglobin after eliminating individual differences, and the calculation method is as follows:
PL＝PAPWS/PAnormal (1)
PAPWSmean intensity of photoacoustic signal of diseased tissue, from PAPWS＝VROL/Vnoise_ROLAnd (4) calculating. Wherein, VROLMean intensity of photoacoustic signal of effective region on photoacoustic image of vascular disease tissue, Vnoise_ROLThe average intensity of the photoacoustic signals of the noise area on the photoacoustic image of the vascular disease tissue is shown.
PAnormalAverage intensity of photoacoustic signal for normal tissue on opposite side, from PAnormal＝VCHR/Vnoise_CHRAnd (4) calculating. Wherein, VCHRThe average intensity of the photoacoustic signal of the effective area on the photoacoustic image of the normal tissue on the opposite side, Vnoise_CHRThe average intensity of the photoacoustic signals of the noise area on the photoacoustic image of the contralateral normal tissue is shown.
The PLR changes from 0-100%, is the hemoglobin density variation of lesion areas in different treatment stages, reflects the dynamic change condition of treatment effect, and is calculated by the following method:
PLpremean intensity of photoacoustic signal, PL, for the diseased tissue before treatmentpostFor the treatment ofThe average intensity of the photoacoustic signal of the diseased tissue at the current time point later.
Example 2
The purpose is as follows: the method of example 1 was used to quantitatively assess the severity and efficacy of nevus flammeus disease (PWS).
The method comprises the following steps: this randomized self-half-face control study included 35 patients with port lentigo rubra. A multi-time node prospective study was performed in 4 out of 35 patients; 5 patients participated in the follow-up evaluation of single-course HMME-PDT treatment efficacy.
The specific scheme is as follows: the method comprises the steps of performing photoacoustic imaging acquisition on lesion parts and contralateral healthy parts of 35 patients respectively before treatment, establishing corresponding PWS grade parameters, performing PWS grade acquisition on the patients participating in prospective study follow-up and curative effect follow-up according to time nodes of the patients immediately after treatment, 1 week, 2 weeks, 4 weeks and 8 weeks after treatment, and establishing PLR (PWS Level reduction) parameters on the basis of the PWS grades before treatment and 8 weeks after treatment for the patients participating in curative effect follow-up to finish quantitative evaluation on curative effect.
As a result: a total of 35 patients completed the study.
As shown in fig. 2, the mean PWS rating was 28.30 ± 12.96% higher for patients over 18 years of age than for patients under 18 years of age (P < 0.01). As shown in FIG. 3, the mean PWS level was 21.30. + -. 9.90% higher in the purple-red group than in the red group (P < 0.01). As shown in fig. 4, based on the results of 5 patients successfully completing the 2-month follow-up, the mean PLR was 49.30 ± 9.50% (P <0.01), with data stability significantly due to traditional subjective evaluation.
The foregoing detailed description of the preferred embodiments of the invention has been presented. It should be understood that numerous modifications and variations could be devised by those skilled in the art in light of the present teachings without departing from the inventive concepts. Therefore, the technical solutions available to those skilled in the art through logic analysis, reasoning and limited experiments based on the prior art according to the concept of the present invention should be within the scope of protection defined by the claims.
Claims (10)
1. A method of processing a photoacoustic image, comprising the steps of:
the method comprises the following steps: irradiating a target object and a reference object by multi-wavelength light pulses, wherein the target object emits a first photoacoustic signal, and the reference object emits a second photoacoustic signal;
step two: receiving and processing a first photoacoustic signal to obtain a first photoacoustic image; receiving and processing a second photoacoustic signal to obtain a second photoacoustic image;
step three: defining a noise area and an effective area in the first photoacoustic image and the second photoacoustic image respectively, and reading and calculating the average intensity of photoacoustic signals in the noise area and the effective area;
step four: and carrying out data processing on the average intensity of the photoacoustic signals and extracting photoacoustic quantification parameters.
2. A method of processing photoacoustic images as set forth in claim 1, wherein the target object and the reference object are selected from a set of symmetrical positions on the same irradiated object, and the same multi-wavelength light pulse irradiates both the target object and the reference object.
3. The method for processing a photoacoustic image according to claim 1, wherein the irradiated object is a skin or a mucous membrane with blood vessels distributed therein.
4. A photoacoustic image processing method according to claim 1, wherein the multi-wavelength light pulse is emitted from a light pulse generator, a pulsed LD light source, or a pulsed LED light source.
5. A photoacoustic image processing method according to claim 4, wherein said multi-wavelength light pulse comprises wavelengths of 750nm and 850 nm.
6. A photoacoustic image processing method according to claim 4, wherein the multi-wavelength light pulse is emitted from a pulsed LED light source, and has a repetition frequency of 10Hz to 4kHz and a pulse width of 5ns to 100 ns.
7. The method for processing a photoacoustic image according to claim 2, wherein the effective area is: comparing the first photoacoustic image with the second photoacoustic image, one or more regions where photoacoustic signals are significantly enhanced in the first photoacoustic image, and a region of a corresponding location on the second photoacoustic image.
8. The method for processing the photoacoustic image according to claim 7, wherein the average intensity of the photoacoustic signals is: an average value of photoacoustic intensities of a plurality of effective areas on the first photoacoustic image or the second photoacoustic image.
9. A method of processing photoacoustic images according to claim 8, wherein the photoacoustic quantification parameter comprises PL, which is calculated by the following equation:
PL＝PAPWS/PAnormal
PAPWSis the average intensity of the photoacoustic signal of the target object, measured by PAPWS＝VROL/Vnoise_ROLCalculating to obtain; wherein, VROLIs the average intensity of the photoacoustic signals of the effective area on the first photoacoustic image, Vnoise_ROLThe average intensity of the photoacoustic signals of the noise area on the first photoacoustic image;
PAnormalaverage intensity of photoacoustic signal of the reference object, by PAnormal＝VCHR/Vnoise_CHRIs calculated to obtain, wherein, VCHRIs the average intensity of the photoacoustic signals of the effective area on the second photoacoustic image, Vnoise_CHRIs the average intensity of the photoacoustic signals of the noise region on the second photoacoustic image.
10. The method for processing photoacoustic images of claim 9, wherein the photoacoustic quantification parameter further comprises PLR, the PLR varying from 0-100%, the PLR being calculated by the following formula:
PLpreis the average intensity of the photoacoustic signal, PL, of the target object at the first detection time pointpo,tThe average intensity of the photoacoustic signal of the target object at the second detection time point is obtained.
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