CN112535531B - Biological tissue welding effect detection device - Google Patents
Biological tissue welding effect detection device Download PDFInfo
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- CN112535531B CN112535531B CN202011355569.1A CN202011355569A CN112535531B CN 112535531 B CN112535531 B CN 112535531B CN 202011355569 A CN202011355569 A CN 202011355569A CN 112535531 B CN112535531 B CN 112535531B
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
- A61B2018/00619—Welding
Abstract
The invention discloses a method and a device for detecting the welding effect of biological tissues, wherein the method comprises the steps of emitting laser scanning signals to the biological tissues to be detected; receiving photoacoustic signals excited by the biological tissues receiving the laser scanning signals by using an air-coupled ultrasonic transducer; determining a first photoacoustic image of the biological tissue from the photoacoustic signals; determining a welding effect of the biological tissue from the first photoacoustic image. The method and the device can quickly and accurately realize the detection of the welding effect of the biological tissue and can be widely applied to the detection field.
Description
Technical Field
The invention relates to the field of detection, in particular to a device for detecting the welding effect of biological tissues.
Background
Biological tissue welding is a novel tissue suturing means, and the molecular structure of the connected tissue is induced to generate thermal change through laser or current energy, so that the minimally invasive surgery of the broken end of the tissue is connected. Compared with needle and thread suture, the technology has the advantages of easy operation, short operation, light inflammation, fast healing, light scar and the like, and has more obvious effect on the tissues such as skin, blood vessels, intestinal tracts and the like which are easy to operate. The biological tissue laser welding technology has great potential and wide development prospect. However, the existing detection method for the welding effect of biological tissues still has some defects, and the detection method for the welding effect of biological tissues mainly depends on the following two methods: welding the surface by direct observation; or tissue welds were sampled and evaluated by staining of the sections. The judgment by observing the surface may have errors, for example, the welding on the surface is successful, but the welding effect is not good in depth, and the judgment error may affect the healing of the wound; although the biological tissue section detection mode is accurate, the whole process is material-taking, the time consumption for dyeing, photographing and observing is long, and the detection of the welding effect cannot be rapidly carried out. Therefore, the above-mentioned method for detecting the welding effect of biological tissue cannot rapidly and accurately judge the welding effect.
Disclosure of Invention
The present invention is directed to solving at least one of the problems of the prior art. Therefore, the invention provides a method and a device for detecting the welding effect of the biological tissue, which can quickly, accurately and conveniently detect the welding effect of the biological tissue.
According to the embodiment of the first aspect of the invention, the method for detecting the welding effect of the biological tissue comprises the following steps:
emitting a pulse laser scanning signal to a biological tissue to be detected;
receiving a photoacoustic signal excited by the biological tissue receiving the pulse laser scanning signal by using an air-coupled ultrasonic transducer;
determining a first photoacoustic image of the biological tissue from the photoacoustic signals;
determining a welding effect of the biological tissue from the first photoacoustic image.
Optionally, the emitting a pulsed laser scanning signal to the biological tissue to be detected specifically includes:
emitting a pulsed laser signal;
and inputting the pulse laser signal to a scanning platform to obtain the laser scanning signal.
Optionally, the inputting the pulsed laser signal to a scanning platform to obtain the laser scanning signal includes: and filtering and shaping the pulse laser signal, and inputting the filtered and shaped pulse laser signal to the scanning platform to obtain the pulse laser scanning signal.
Optionally, the standard photoacoustic image is a previously stored photoacoustic image of normal biological tissue.
Optionally, the determining the welding effect of the biological tissue from the first photoacoustic image comprises:
acquiring a standard photoacoustic image and a difference threshold;
determining image difference data from the first photoacoustic image and the standard photoacoustic image;
comparing the image difference data with the difference threshold to determine the welding effect of the biological tissue.
The detection method provided by the embodiment of the invention at least has the following beneficial effects: the embodiment of the invention comprises the air coupling ultrasonic transducer for receiving the characteristics of the photoacoustic signal excited by laser irradiation of the welded biological tissue to be detected, realizes the non-contact imaging of the welded biological tissue to be detected by means of air coupling photoacoustic imaging, and then judges the welding effect according to the obtained photoacoustic image. Because the air coupling photoacoustic imaging technology is adopted, the method can detect the welding effect without contacting with the welded biological tissue, and meanwhile, the speed of photoacoustic imaging is faster than that of slice dyeing judgment detection results, so that the detection conclusion can be quickly, accurately and conveniently obtained.
According to another aspect of the present invention, an apparatus for detecting welding effect of biological tissue is characterized by comprising:
the laser generating module is used for transmitting a pulse laser signal;
the scanning module is connected with the laser generating module and used for receiving the pulse laser signal and outputting a pulse laser scanning signal;
the signal acquisition and processing module comprises an air coupling ultrasonic transducer and a signal amplifier which are connected with each other; the air coupling ultrasonic transducer is used for receiving a photoacoustic signal excited by the pulse laser scanning signal of the biological tissue to be detected and converting the photoacoustic signal into a first electric signal; the amplifier receives the first electric signal, amplifies the first electric signal and outputs a second electric signal;
and the control module is connected with the amplifier in the signal acquisition and processing module and used for receiving the second electric signal, determining a first photoacoustic image of the biological tissue according to the second electric signal and determining the welding effect of the biological tissue according to the first photoacoustic image.
Alternatively, the first and second liquid crystal display panels may be,
the laser generation module comprises a pulse laser and a laser shaping module;
the pulse laser is used for transmitting a first pulse laser signal;
the laser shaping module comprises a neutral density optical filter, a space optical shaping assembly and an optical fiber collimator;
the first pulse laser signal sequentially passes through the neutral density filter, the spatial light shaping assembly and the optical fiber collimator to obtain the pulse laser signal; the optical fiber collimator is connected with the scanning module.
Optionally, the detection apparatus further includes a programmable array module, where the programmable array module is configured to output a timing signal, and the timing signal is respectively input to the pulse laser, the scanning module, and the control module, and is respectively configured to control the pulse laser to generate a first pulse laser signal, control the scanning module to perform laser scanning, and control the control module to collect the second electrical signal.
Optionally, the standard photoacoustic image is a previously stored photoacoustic image of normal biological tissue.
Optionally, the determining the welding effect of the biological tissue from the first photoacoustic image comprises:
determining image difference data from the first photoacoustic image and a standard photoacoustic image;
and comparing the image difference data with a difference threshold value to determine the welding effect of the biological tissue.
The detection device provided by the embodiment of the invention at least has the following beneficial effects: the embodiment of the invention comprises the steps that the air coupling ultrasonic transducer is used for receiving the characteristics of the photoacoustic signal excited by laser irradiation of the welded biological tissue to be detected, so that the non-contact imaging of the welded biological tissue to be detected is realized by means of air coupling photoacoustic imaging, then the welding effect is judged according to the obtained photoacoustic image, and the detection conclusion can be quickly, accurately and conveniently obtained.
Drawings
The above and/or additional aspects and advantages of the present invention will become apparent and readily appreciated from the following description of the embodiments, taken in conjunction with the accompanying drawings of which:
FIG. 1 is a schematic flow chart of a detection method according to an embodiment of the present invention;
FIG. 2 is a schematic view of the detecting device of the present invention.
Detailed Description
Reference will now be made in detail to embodiments of the present invention, examples of which are illustrated in the accompanying drawings, wherein like or similar reference numerals refer to the same or similar elements or elements having the same or similar function throughout. The embodiments described below with reference to the accompanying drawings are illustrative only for the purpose of explaining the present invention, and are not to be construed as limiting the present invention.
In the description of the present invention, it should be understood that the orientation or positional relationship referred to in the description of the orientation, such as the upper, lower, front, rear, left, right, etc., is based on the orientation or positional relationship shown in the drawings, and is only for convenience of description and simplification of description, and does not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and thus, should not be construed as limiting the present invention.
In the description of the present invention, the meaning of a plurality of means is one or more, the meaning of a plurality of means is two or more, and larger, smaller, larger, etc. are understood as excluding the number, and larger, smaller, inner, etc. are understood as including the number. If the first and second are described for the purpose of distinguishing technical features, they are not to be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated or implicitly indicating the precedence of the technical features indicated.
The photoacoustic imaging (PAI) is a biological imaging technology based on the difference of light absorption and using photoacoustic wave (i.e. ultrasonic wave) as information carrier. When biological tissues are irradiated by short pulse laser, the tissue absorbs light energy and generates heat, so that the temperature of a laser irradiation point changes to be instantaneously thermally expanded, and ultrasonic waves are radiated outwards. The phenomenon that the light is excited to generate ultrasound is a photoacoustic effect, the generated ultrasonic signal is a photoacoustic signal, and after the photoacoustic signal is received by an ultrasonic detector, the light absorption distribution in the tissue is reconstructed by an algorithm, namely photoacoustic imaging. Photoacoustic imaging is a non-invasive imaging technique that is non-destructive. When the pulse laser excites the biological tissue, the ultrasonic wave is generated as an information carrier, and the optical absorption distribution image of the biological tissue is reconstructed by receiving the ultrasonic wave signal, so that the method is a non-ionization and non-invasive non-destructive imaging means. The imaging can be excited by utilizing a plurality of wavelengths by utilizing the spectrum selective absorption difference of the biological tissue, and the obtained differentiated photoacoustic signals can reflect the structure and function of the tissue and the multi-dimensional information such as the blood oxygen saturation and the like. The photoacoustic imaging combines the advantages of high contrast of optical imaging and high penetration depth of ultrasonic imaging, penetrates deeper than pure optical imaging, can break through the soft limit (1 mm) of the optical imaging depth of penetration optics such as laser confocal microscopic imaging, optical coherence tomography and the like, and can be used for imaging deep tissues.
Photoacoustic imaging technology is currently widely used in Photoacoustic Tomography (PAT) and Photoacoustic microscopy (PAM). Photoacoustic tomography is the most developed technology in the field of photoacoustic imaging at present, and the technology has been widely applied in the biomedical field at present. PAT can create multi-scale, multi-contrast images of various biological structures from organelles to organs. This emerging technology overcomes the high scattering of photons in biological tissue by exploiting the photoacoustic effect. The molecules absorb light to generate heat to cause pressure jumps, thereby generating ultrasonic waves which are received by an acoustic detector and reconstructed to obtain an image. PAT can provide structural, functional, molecular, hemodynamic, oxygen metabolism, biomarkers and gene expression studies. PAM is another commonly used photoacoustic imaging mode, and similar to the operating principle of an optical microscope, a photoacoustic microscope focuses pulse laser on the surface of an object to be measured through an objective lens to excite and generate photoacoustic signals, and simultaneously uses a focused ultrasonic transducer to detect the excited photoacoustic signals. An important application of photoacoustic microscopic imaging is to image capillaries, so that the information of the shapes, structures, functions and the like of the capillaries can be obtained, and a new means is provided for researching the microvascular lesions.
The photoacoustic tomography is suitable for imaging large-area tissues with high requirements on depth, and the photoacoustic microscopy is mainly suitable for imaging local tissues with high resolution. Different photoacoustic imaging modes can be targeted for different tissue welding sites. For example, a photoacoustic tomography mode can be used for evaluating the tissue welding effect of a large wound on the abdomen or other parts, so that the welding effect can be quickly evaluated in a large area; and the photoacoustic microscopic mode can be used for imaging for tissue welding of a tiny part, such as tissue welding of a blood vessel, so that high-resolution imaging can be performed on the welding effect of the tiny part, and the welding effect can be judged.
As shown in FIG. 1, the method for detecting welding effect of biological tissue of the present invention comprises the following steps:
s110, emitting a pulse laser scanning signal to a biological tissue to be detected;
s120, receiving a photoacoustic signal excited by the biological tissue receiving the pulse laser scanning signal by using an air-coupled ultrasonic transducer;
s130, determining a first photoacoustic image of the biological tissue according to the photoacoustic signals;
s140, determining the welding effect of the biological tissue according to the first photoacoustic image.
Wherein the biological tissue to be detected is biological tissue which has been welded. At present, a receiving device of a photoacoustic signal in a photoacoustic imaging system is an ultrasonic transducer, a couplant or a coupling module is required for transmitting a conventional photoacoustic signal to the ultrasonic transducer, but when tissue welding is performed, the couplant or the coupling module is used to contact with a welding part, which may cause infection or other consequences of the welding part, so that in the embodiment, the ultrasonic transducer capable of being coupled with air is used to receive the photoacoustic signal, thereby avoiding adverse effects caused by the need of the couplant.
Alternatively, the pulsed laser scanning signal in step S110 may be obtained by the pulsed laser signal via a scanning module. After passing through the scanning module, scanning laser needed by the photoacoustic tomography or photoacoustic microscopic imaging technology can be selected according to the characteristics of the welding part of the biological tissue to be detected. The emitted pulsed laser signal needs to have a certain wavelength, the penetration depth of the laser light is different for different wavelengths, and different wavelengths can be used when imaging different biological tissues, including but not limited to the following wavelengths 532nm, 1064nm, 660nm, etc.
Optionally, the inputting the pulsed laser signal to a scanning platform to obtain the laser scanning signal includes: and filtering and shaping the pulse laser signal, and inputting the filtered and shaped pulse laser signal to the scanning module to obtain the laser scanning signal. After the pulse laser is emitted, the pulse laser is shaped, filtered and focused by an optical element and is used for subsequent photoacoustic imaging excitation. The size and waveform energy of the laser beam can meet the requirements of photoacoustic imaging through optical shaping, filtering, focusing and other processing. After the pulse laser is emitted by a pulse laser, stray light is firstly filtered, and different optical filters are selected for lasers with different wavelengths; the appropriate laser light is then output through an appropriate aperture. For the photoacoustic tomography system, the filtered and shaped target pulse laser is focused through a cylindrical lens or directly scans the biological tissue welding part through a scanning module; for the photoacoustic microscopy system, the pulse laser after filtering and shaping can be spatial light directly focused through a focusing element, or the shaped pulse laser enters an optical fiber after being coupled through an optical fiber coupling system and then enters a scanning module after being focused through the focusing element, so that the biological tissue welding part is scanned and excited.
Optionally, the determining the welding effect of the biological tissue from the first photoacoustic image comprises:
acquiring a standard photoacoustic image and a difference threshold;
determining image difference data from the first photoacoustic image and the standard photoacoustic image;
comparing the image difference data to the difference threshold to determine the welding effect of the biological tissue.
In the present embodiment, the first photoacoustic image generated for the welding site of the biological tissue and the photoacoustic image of the normal biological tissue are compared to obtain difference data therebetween, and the difference data is compared with a preset difference threshold value to determine the welding effect of the biological tissue to be measured. For example, when the difference data is greater than the difference threshold, it can be determined that the welding effect is not good and further processing is required; and if the difference data is less than or equal to the difference threshold value, judging that the welding effect is good. Such a determination is advantageous for achieving a determination of the welding effect in an automated manner. It will be appreciated by those skilled in the art that the determination may also be made directly from the first photoacoustic image.
Optionally, the standard photoacoustic image is a previously stored photoacoustic image of normal biological tissue.
The standard photoacoustic image is a photoacoustic image of normal biological tissue. Can be generated and stored by imaging a laser scan of normal biological tissue in advance.
The photoacoustic images are different for different welding sites and different photoacoustic imaging modes can be employed for different tissue welding sites. For example, the photoacoustic tomography mode can be used for evaluating the tissue welding effect of a large wound on the abdomen or other parts, so that the welding effect can be quickly evaluated in a large area; and the photoacoustic microscopic mode can be used for imaging for tissue welding of a tiny part, such as tissue welding of a blood vessel, so that high-resolution imaging can be performed on the welding effect of the tiny part, and the welding effect can be judged.
The embodiment of the invention provides a biological tissue welding effect detection device, which comprises:
the laser generating module is used for transmitting a pulse laser signal;
the scanning module is connected with the laser generating module and used for receiving the pulse laser signal and outputting a pulse laser scanning signal;
the signal acquisition and processing module comprises an air coupling ultrasonic transducer and a signal amplifier which are connected with each other; the air coupling ultrasonic transducer is used for receiving a photoacoustic signal excited by the irradiation of the laser signal to the biological tissue to be detected and converting the photoacoustic signal into a first electric signal; the amplifier receives the first electric signal, amplifies the first electric signal and outputs a second electric signal;
and the control module is connected with the amplifier in the signal acquisition and processing module and used for receiving the second electric signal, determining a first photoacoustic image of the biological tissue according to the second electric signal and determining the welding effect of the biological tissue according to the first photoacoustic image.
Optionally, the control module may include a computer, and acquire the second electrical signal transmitted by the signal acquisition and processing module, and reconstruct an image according to the second electrical signal to obtain a photoacoustic image, and then analyze the photoacoustic image to determine the welding effect of the biological tissue.
Alternatively,
the laser generation module comprises a pulse laser and a laser shaping module;
the pulse laser is used for emitting a pulse laser signal;
the laser shaping module comprises a neutral density optical filter, a space optical shaping assembly and an optical fiber collimator;
the pulse laser signal sequentially passes through the neutral density optical filter, the spatial light shaping assembly and the optical fiber collimator to obtain the pulse laser signal; the optical fiber collimator is connected with the scanning module.
And filtering and shaping the pulse laser signal through a laser shaping module to obtain a proper target light beam.
Optionally, the detection apparatus further includes a programmable array module, where the programmable array module is configured to output a timing signal, and the timing signal is input to the pulse laser, the scanning module, and the control module, respectively.
And time sequence signals are uniformly distributed through the programmable display modules and used as clock control to coordinate the work of each module to complete the detection task.
Optionally, the determining the welding effect of the biological tissue from the first photoacoustic image comprises:
determining image difference data from the first photoacoustic image and a standard photoacoustic image;
comparing the image difference data with a difference threshold to determine the welding effect of the biological tissue.
Optionally, the standard photoacoustic image is a previously stored photoacoustic image of normal biological tissue.
The effect of the corresponding features in the biological tissue welding effect detection device is consistent with that in the biological tissue welding effect detection method.
Fig. 2 shows a specific example of a biological tissue welding effect detection apparatus, which includes a pulse laser 1, a neutral density filter 2, a first lens 3, a pinhole element 4, a second lens 5, an optical fiber collimator 6, a scanning module 7, a biological tissue 8 to be detected, an air-coupled ultrasonic transducer 9, an amplifier 10, a control module 11, and a programmable array module 12. The first lens 3, the pinhole element 4 and the second lens 5 form a space light shaping component, and the pulse laser 1, the neutral density filter 2, the space light shaping component and the optical fiber collimator 6 form a laser generation module. The dotted line in fig. 2 represents light transmission, and the dotted line with an arrow represents electric signal transmission.
After the pulse laser outputs pulse laser, stray light is firstly filtered through a band-pass filter, different filters are selected for the laser with different wavelengths, and then the pulse laser outputs proper laser through a proper diaphragm. For the photoacoustic tomography system, the filtered and shaped target pulse laser is focused through a cylindrical lens or is directly scanned by a laser scanning system to scan the biological tissue welding part; for the photoacoustic microscopy system, the pulse laser after filtering and shaping can be spatial light directly focused by a focusing element, or the shaped pulse laser is coupled by an optical fiber coupling system, is subjected to optical fiber, is focused by the focusing element and then enters a laser scanning system to scan and excite the welding part of the biological tissue. The above elements including but not limited to optical filters, diaphragms, focusing lenses, etc., various convex lenses, grin lenses, C-lenses are all within the scope of the focusing lens.
The scanning module drives a focusing light beam to scan the biological tissue welding part through the scanning system, so that photoacoustic excitation of an interested region is realized to obtain a photoacoustic image, and the scanning module can be realized by but not limited to the following modes: irradiating the focused space light onto a galvanometer, and driving a light beam to scan the region of interest through a two-dimensional galvanometer; or transmitting a pulsed laser through an optical fiber.
The amplifier is used for collecting and amplifying the photoacoustic signals and sending the photoacoustic signals to the control module for image processing. When the air coupling ultrasonic transducer outputs an electric signal, the electric signal is amplified by the amplifier, filtered by the filter (not shown in the figure), and subjected to data acquisition by the high-speed data acquisition card (not shown in the figure) and then output to the control module. The air coupling ultrasonic transducer can realize non-contact photoacoustic signal acquisition without coupling medium, and avoids pollution to tissue welding parts. The signal amplifier can realize the amplification of weak signals, and the signal filter can reduce various possible noise interferences, so that the signal-to-noise ratio of the photoacoustic signal is improved, and convenience is provided for the reconstruction of the photoacoustic signal image.
The control module processes the obtained electric signals converted from the photoacoustic signals to realize image reconstruction, and obtains corresponding photoacoustic images through an algorithm for detecting the tissue welding effect. The control module may include a data processing module, a GPU module, a software module, and the like.
The control module may include a computer that may cooperate with associated hardware and software, such as a programmable logic array module, or Labview, to implement the various modules.
It will be understood that all or some of the steps, systems of methods disclosed above may be implemented as software, firmware, hardware, and suitable combinations thereof. Some or all of the physical components may be implemented as software executed by a processor, such as a central processing unit, digital signal processor, or microprocessor, or as hardware, or as an integrated circuit, such as an application specific integrated circuit. Such software may be distributed on computer readable media, which may include computer storage media (or non-transitory media) and communication media (or transitory media). The term computer storage media includes volatile and nonvolatile, removable and non-removable media implemented in any method or technology for storage of information such as computer readable instructions, data structures, program modules or other data, as is well known to those of ordinary skill in the art. Computer storage media includes, but is not limited to, RAM, ROM, EEPROM, flash memory or other memory technology, CD-ROM, Digital Versatile Disks (DVD) or other optical disk storage, magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices, or any other medium which can be used to store the desired information and which can accessed by a computer. In addition, communication media typically embodies computer readable instructions, data structures, program modules or other data in a modulated data signal such as a carrier wave or other transport mechanism and includes any information delivery media as is well known to those skilled in the art.
The embodiments of the present invention have been described in detail with reference to the accompanying drawings, but the present invention is not limited to the above embodiments, and various changes can be made within the knowledge of those skilled in the art without departing from the gist of the present invention.
Claims (4)
1. A welding effect detection device for biological tissues is characterized by comprising:
the laser generating module is used for transmitting a pulse laser signal; filtering and shaping the pulse laser signal; the wavelength of the pulse laser signal is specifically set according to biological tissues, and the set wavelength comprises 532nm, 1064nm and 660 nm;
the scanning module is connected with the laser generating module and used for receiving the pulse laser signal and outputting a pulse laser scanning signal to the region of interest; the scanning module drives a pulse laser scanning signal to scan the biological tissue welding part through a scanning system;
the signal acquisition and processing module comprises an air coupling ultrasonic transducer and a signal amplifier which are connected with each other; the air coupling ultrasonic transducer is used for receiving a photoacoustic signal excited by the pulse laser scanning signal of the biological tissue to be detected and converting the photoacoustic signal into a first electric signal; the signal amplifier is used for receiving the first electric signal, amplifying the first electric signal and outputting a second electric signal;
the control module is connected with the amplifier in the signal acquisition and processing module and used for receiving the second electric signal, determining a first photoacoustic image of the biological tissue according to the second electric signal and determining the welding effect of the biological tissue according to the first photoacoustic image;
the determining the welding effect of the biological tissue from the first photoacoustic image includes:
determining image difference data from the first photoacoustic image and a standard photoacoustic image;
and comparing the image difference data with a difference threshold value to determine the welding effect of the biological tissue.
2. The detection device according to claim 1, wherein:
the laser generation module comprises a pulse laser and a laser shaping module;
the pulse laser is used for emitting a pulse laser signal;
the laser shaping module comprises a neutral density optical filter, a space optical shaping assembly and an optical fiber collimator;
the pulse laser signal sequentially passes through the neutral density filter, the spatial light shaping assembly and the optical fiber collimator to obtain a filtered and shaped pulse laser signal; the optical fiber collimator is connected with the scanning module.
3. The detection device according to claim 2, wherein:
the detection device further comprises a programmable array module, wherein the programmable array module is used for outputting a time sequence signal, the time sequence signal is respectively input to the pulse laser, the scanning module and the control module, and is respectively used for controlling the pulse laser to generate a pulse laser signal, controlling the scanning module to carry out laser scanning and controlling the control module to collect the second electric signal.
4. The detection device according to claim 1, wherein: the standard photoacoustic image is a previously stored photoacoustic image of a normal biological tissue.
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