Uterine salpingography imaging device and method

Abstract

The invention is suitable for the field of medical imaging, and provides a hysterosalpingography imaging device and method, and the method comprises the following steps: S1, examinee preparation, S2, preparation before imaging, S3, ultrasonic imaging, S4, photoacoustic contrast imaging, and S5, image fusion. According to the imaging method, the photoacoustic imaging technology and the ultrasonic imaging technology are combined, ICG serves as a contrast agent, a high-resolution uterine fallopian tube structure image can be obtained, functional parameters such as blood flow information and blood oxygen information in tissue can be detected through ultrasonic and photoacoustic characteristics, the imaging range is larger by designing a movable area array probe, and the imaging accuracy is improved. The operation is more convenient.

Description

Technical Field

[0001] The present invention relates to the field of medical imaging and is applicable to the imaging of the uterine fallopian tubes in the female reproductive system. It is a dual-modal imaging technology based on photoacoustic imaging and ultrasonic imaging. Specifically, it is a method of planar array non-radiative photoacoustic-ultrasonic dual-modal imaging of the uterine fallopian tubes, combined with indocyanine green (ICG) as a photoacoustic contrast agent to achieve high-resolution structural and functional imaging of the uterine fallopian tubes. Background Art

[0002] Hysterosalpingography is a key method clinically used to evaluate the health status of the female reproductive system. Traditional hysterosalpingography usually relies on X-ray technology, such as hysterosalpingography (HSG). Although this technology can provide accurate structural imaging, it relies on ionizing radiation, increasing the health risks of patients during examination, especially for those who need to undergo multiple examinations. In addition, X-ray imaging technology can only provide structural information of the uterine fallopian tubes and cannot evaluate the functional status of the uterine fallopian tubes in real time, such as blood flow information and blood oxygen information, while the functional status helps to identify whether polyps and tumors have occurred in the fallopian tubes and the uterus. Therefore, there is an urgent need for a non-radiative, safe and effective imaging technology that can provide structural imaging while also obtaining relevant functional information.

[0003] Currently, another commonly used clinical imaging technology for hysterosalpingography is hysterosalpingo-ultrasound graphy (HSUG), which uses a microbubble contrast agent (commonly SonoVu) injected through the vagina to image the cervical fallopian tubes. Compared with HSG, the HSUG technology has the characteristics of non-radiation and high cost performance, but its imaging resolution and contrast are still limited, and it may miss the diagnosis of cases where there is a blockage in a fine area. Therefore, a high-resolution imaging method is needed to supplement more detailed information.

[0004] Photoacoustic imaging is one of the popular new imaging technologies at home and abroad in recent years and has developed rapidly. Photoacoustic imaging combines the contrast of optics and the penetration depth of acoustics. It can not only provide high-resolution structural information of the scanned part, but also provide functional metabolic information obtained based on tissue multi-spectral absorption, quantitatively reflecting the content of different biomolecules (such as hemoglobin, melanin, lipids, etc.) in the tissue in real time, and at the same time has multiple advantages such as non-invasiveness, non-ionizing radiation, and functional imaging. Using photoacoustic imaging technology can make up for the limitations of the above-mentioned commonly used hysterosalpingography imaging methods and provide more reference information for the examination of the uterine fallopian tubes. Summary of the Invention

[0005] In view of the problems in the related technologies mentioned above, the present invention proposes a photoacoustic-ultrasonic dual-modal imaging method, which is specially designed for uterine tube imaging, to overcome the problems existing in the existing related technologies and achieve high-resolution structural and functional imaging of the uterine tubes.

[0006] The present invention is realized through the following technical solutions:

[0007] The present invention relates to a uterine tube contrast imaging device and an imaging method. This imaging method combines photoacoustic imaging and ultrasonic imaging technologies, uses ICG as a contrast agent, can not only obtain high-resolution structural images of the uterine tubes, but also detect functional metabolic parameters in tissues, such as blood flow information and blood oxygen information, through ultrasonic and photoacoustic characteristics, and designs a movable planar array probe to make the imaging range larger and the operation more convenient. The related technical method includes the following steps:

[0008] S1. Preparation of the examiner: The examination date is selected within three to eight days after the end of menstruation. After gynecological examination and inquiry, it is determined that the examiner has no relevant gynecological diseases and acute inflammations.

[0009] S2. Preparation before imaging: It includes disinfecting the vagina of the examiner, emptying the bladder, arranging the body position, anesthesia, etc. Then, a catheter is inserted into the cervix from the vagina, and an appropriate amount of physiological saline is injected into the balloon to expand the balloon and seal the cervical os to prevent the contrast agent from leaking during subsequent imaging.

[0010] S3. Ultrasonic imaging: Set the ultrasonic probe parameters required for imaging, select an appropriate imaging section, and perform coronal or sagittal plane imaging of the uterine tubes. Whether to obtain the blood flow information of the scanned area using the Doppler ultrasonic imaging principle can be selected according to the examination requirements.

[0011] S4. Photoacoustic contrast imaging: Switch the ultrasonic imaging module to the photoacoustic imaging module to prepare for subsequent contrast imaging. Inject the prepared ICG solution from the catheter, and record the imaging time of both uterine tubes (starting from the injection of the contrast agent), the adverse reactions of the patient, and the imaging conditions of the uterine tubes. After the injection is completed, the blood oxygen information of the scanned area can be further measured using the dual-wavelength imaging principle.

[0012] S5. Image fusion: The blood flow information can be obtained using the ultrasonic module, and the blood oxygen information can be obtained using the photoacoustic module. The ultrasonic image and the photoacoustic image are superimposed through the image fusion module to jointly display functional information such as blood flow and blood oxygen.

[0013] The said S1 includes the following steps:

[0014] S11. The examiner needs to perform basic gynecological examinations before the angiography according to the doctor's instructions, including checking whether there is inflammation in the leucorrhea and whether the urine test shows pregnancy. The doctor also needs to instruct the examiner to abstain from sexual intercourse and vaginal medication before the angiography, and select the examination date three to eight days after the examiner's menstrual period ends.

[0015] The said S2 includes the following steps:

[0016] S21. Thirty minutes before imaging, inject atropine intramuscularly into the examiner to reduce glandular secretion, empty the bladder, and place the examiner in the lithotomy position with the buttocks elevated by about 10 cm to make the examination site close to the ultrasound probe and improve the imaging quality. Then inject anesthetic to reduce the discomfort of the examiner during imaging.

[0017] The specific operation of injecting the contrast agent from the catheter is as follows. The catheter is designed with two water injection ports and one water outlet. One of the water injection ports is connected to the balloon via a guide wire, and normal saline can be injected through this water injection port to inflate the balloon to seal the cervical os and prevent the leakage of the contrast agent during subsequent angiography imaging. The other water injection port is directly connected to the water outlet and is responsible for sending the contrast agent into the uterine fallopian tubes to achieve subsequent angiography imaging.

[0018] The said S3 includes the following steps:

[0019] S31. Before using the ultrasonic imaging module to image the examiner, first, the scanning parameters of the ultrasonic imaging device need to be set, and appropriate frequency and gain are selected to effectively penetrate the tissue and capture blood flow information.

[0020] S32. Start the ultrasonic imaging device and perform a routine scan of the uterine fallopian tubes. The probe position can be moved arbitrarily to obtain the best imaging section of the uterine fallopian tubes for imaging. The ultrasonic module will display the structural information inside the uterine fallopian tubes. By analyzing the echo signals and using the Doppler effect, information such as blood flow velocity and direction can be obtained.

[0021] The said S4 includes the following steps:

[0022] S41. Start the photoacoustic imaging device and set appropriate parameters to perform angiography imaging on the uterine fallopian tubes. The main excitation wavelength of ICG in aqueous solution is about 780 nm. After binding to proteins in the blood environment, the absorption peak may redshift to 800 nm. Therefore, select 780 - 800 nm as the excitation wavelength range to obtain the best photoacoustic signal and improve the imaging quality of the uterine fallopian tubes.

[0023] S42. Use the dual - wavelength imaging method to measure the blood oxygen information of the uterine fallopian tubes. Image the uterine fallopian tubes after injecting the contrast agent at the same section by switching two wavelengths, and the blood oxygen value of the uterine fallopian tubes can be obtained through calculation.

[0024] S43. Method for measuring blood oxygen information using dual wavelengths: Hemoglobin in the blood is divided into oxyhemoglobin and deoxyhemoglobin, and their light absorption characteristics are different at different wavelengths. By measuring the light absorption of tissues at different wavelengths and the intensity changes of photoacoustic signals, the relative contents of oxyhemoglobin and deoxyhemoglobin can be calculated. Combining these content ratios, the blood oxygen saturation (i.e., the percentage of oxyhemoglobin in the blood) can be further calculated. The calculation formula is as follows:

[0025]

[0026] Among them, C Hbo2 and C Hb represent the relative content ratios of oxyhemoglobin Hbo2 and deoxyhemoglobin Hb respectively. and represent the extinction coefficients of oxyhemoglobin Hbo2 and deoxyhemoglobin Hb at wavelengths and respectively. and represent the intensities of photoacoustic signals obtained at wavelengths and respectively.

[0027] The imaging device proposed by this invention has the following key components:

[0028] 1. Ultrasonic transducer array:

[0029] 512 ultrasonic transducer channels: A high-density ultrasonic transducer array is integrated inside the probe, which contains 512 independent ultrasonic channels, and each channel corresponds to an independent transducer unit. These transducer units are made of piezoelectric materials and can accurately transmit and receive ultrasonic signals. The 512 channels work synchronously, enabling the device to quickly collect ultrasonic echo signals in a large area and generate images of the uterine tube structure, which is applicable to both the ultrasonic imaging module and the photoacoustic imaging module.

[0030] Multi-band working mode: Each ultrasonic channel supports multi-band operation, and the adjustable frequency range is 1 - 40 MHz, ensuring that the device can select and adjust the frequency according to different tissue characteristics during imaging. For example, when imaging deeper tissues, the device can be adjusted to a lower frequency to improve penetration, while for fine imaging of superficial tissues, the device can be adjusted to a higher frequency to provide higher resolution.

[0031] Beamforming Technology: 512 ultrasound transducer channels support advanced beam forming algorithms. The beamforming technology can combine the signals received by multiple channels to generate images with high signal-to-noise ratio and high spatial resolution, which not only improves the imaging accuracy but also reduces image blurring caused by signal attenuation. In addition, the beamforming technology can flexibly adjust the focus of the imaging area to provide deeper tissue images.

[0032] Real-time 3D Imaging: Thanks to the synchronous operation of 512 ultrasound channels, the device can quickly generate real-time 3D images of the uterus and fallopian tubes. This function is particularly important for doctors to evaluate the morphological structure of the uterus and fallopian tubes during examinations. The spatial information provided by 3D imaging can help doctors understand more structural information of the uterus and fallopian tubes, contributing to quickly locating the blocked parts of the uterus and fallopian tubes or diagnosing other lesion positions.

[0033] 2. Laser Emission Unit:

[0034] Laser Emission Unit: The probe integrates a laser emission unit dedicated to photoacoustic imaging, using nanosecond pulsed lasers, and the emitted laser in the wavelength range of 680 - 1064 nm is adjusted through an optical parametric oscillator (OPO). These laser beams are absorbed by chromophores such as hemoglobin in the irradiated area, generating instantaneous thermoelastic expansion, and then generating ultrasonic signals. The ultrasonic signals are synchronously collected and processed through 512 ultrasound transducer channels to generate high-resolution photoacoustic images.

[0035] Photoacoustic Imaging Time Synchronization Control: The device adopts high-precision clock synchronization control to ensure the precise matching of the time points of laser pulse emission and ultrasonic signal reception, achieving complete synchronization of photoacoustic imaging.

[0036] Photoacoustic Signal Enhancement: To improve the sensitivity of photoacoustic signals, the probe is designed with multiple laser beam emission points to ensure uniform laser irradiation on the target tissue area. By combining beamforming technology, weak photoacoustic signals are enhanced, enabling the effective detection of signals from low-concentration hemoglobin or other absorbing chromophores, thereby further improving the image quality.

[0037] 3. Photoacoustic and Ultrasound Dual-Mode Fusion:

[0038] The core control unit in the probe can fuse photoacoustic signals and ultrasonic signals in real time. Photoacoustic signals provide high-contrast images and capture the blood oxygen information of the uterus and fallopian tubes, while ultrasonic signals provide detailed anatomical structures and blood flow information of tissues. These two modes superimpose the ultrasonic image and the photoacoustic image through image processing algorithms to generate a fused image, enabling doctors to observe the anatomical structure, blood flow status, and blood oxygen function of the uterus and fallopian tubes on the same interface, improving the diagnostic accuracy and efficiency.

[0039] 4. Computer processing system:

[0040] The computer processing system allows the operator to select the ultrasound imaging or photoacoustic imaging mode on it, set the relevant parameters required for imaging, such as wavelength, energy, frequency, gain, etc., perform real-time imaging based on the collected data and display it on the screen, and can choose whether to save it by itself. Moreover, there is relevant software on the system to calculate functional information such as blood flow and blood oxygen.

[0041] The present invention has the following advantages:

[0042] 1. High-resolution imaging: 512 ultrasound transducer channels and the optical resolution using photoacoustic imaging provide extremely high image resolution, enabling doctors to clearly see the fine structures of the fallopian tubes and surrounding tissues, and is particularly suitable for diagnosing problems such as fallopian tube stenosis and obstruction.

[0043] 2. Functional imaging: The dual-modal imaging technology of photoacoustic and ultrasound not only provides structural information but also can detect functional information such as blood flow and blood oxygen saturation in real time, helping doctors more comprehensively evaluate the functional status of the fallopian tubes, and is particularly beneficial for doctors to judge whether polyps or tumors are generated in the uterine appendages.

[0044] 3. Radiation-free and repeatable operation: This device is completely radiation-free and suitable for repeated use in the short term, greatly reducing the examination risk for patients who need multiple examinations.

[0045] 4. Reducing female pain: The movable probe design and non-invasive examination methods reduce the discomfort of the examinee during the hysterosalpingography imaging process and improve the comfort of the examinee during the examination. BRIEF DESCRIPTION OF THE DRAWINGS

[0046] In order to more clearly illustrate the technical solutions implemented in the invention, the drawings required for describing the embodiments will be briefly introduced below.

[0047] Figure 1 FIG. is the examination flow chart for performing hysterosalpingography imaging on an examinee using the planar array radiation-free hysterosalpingo photoacoustic ultrasound dual-modal imaging method.

[0048] Figure 2 FIG. is a schematic diagram of a catheter for injecting a contrast agent into the fallopian tubes from the vagina.

[0049] Figure 2 In the figure: 1. Water injection port 1, 2. Water injection port 2, 3. Guide wire, 4. Water outlet, 5. Balloon.

[0050] Figure 3 FIG. is a schematic diagram of the device for the planar array radiation-free hysterosalpingo photoacoustic ultrasound dual-modal imaging method.

[0051] Figure 3 Among them: 1. Examination bed, 2. Ultrasonic transducer, 3. Telescopic shaft, 4. Robot arm, 5. Water bag, 6. Laser coupling optical path, 7. Adapter, 8. Display screen, 9. Operating console, 10. Computer mainframe and laser emitter are integrated as a whole. Specific implementation mode

[0052] Next, the technical solutions in the invention embodiments will be described in detail and clearly in conjunction with the accompanying drawings in the invention embodiments.

[0053] As Figure 1 shown, the steps of performing hysterosalpingography imaging on the examinee by using the technical solution proposed by the present invention are as follows:

[0054] S1. Examinee preparation: Select the examination date within three to eight days after the end of menstruation. After gynecological examination and inquiry, it is determined that the examinee has no relevant gynecological diseases and acute inflammation.

[0055] S2. Preparation before imaging: Include vaginal disinfection of the examinee, emptying the bladder, body position placement, anesthesia, etc. Then insert a catheter into the cervix through the vagina, inject an appropriate amount of physiological saline into the balloon to expand the balloon and seal the cervical os to prevent leakage of the contrast agent during subsequent imaging.

[0056] S3. Ultrasonic imaging: Set the ultrasonic probe parameters required for imaging, select an appropriate imaging section, perform coronal or sagittal imaging on the uterus and fallopian tubes, and whether to use the Doppler ultrasonic imaging principle to obtain the blood flow information of the scanned area can be selected according to the examination requirements.

[0057] S4. Photoacoustic contrast imaging: Switch the ultrasonic imaging module to the photoacoustic imaging module to prepare for subsequent contrast imaging. Inject the prepared ICG solution through the catheter, record the imaging time of the bilateral uterus and fallopian tubes (counting from the start of injecting the contrast agent), the adverse reactions of the patient, and the imaging conditions of the uterus and fallopian tubes. After the injection is completed, the double-wavelength imaging principle can be further used to measure the blood oxygen information of the scanned area.

[0058] S5. Image fusion: The blood flow information can be obtained by using the ultrasonic module, and the blood oxygen information can be obtained by using the photoacoustic module. The ultrasonic image and the photoacoustic image are superimposed through the image fusion module to jointly display functional information such as blood flow and blood oxygen.

[0059] The said S1 includes the following steps:

[0060] S11. The examinee needs to perform basic gynecological examinations before angiography according to the doctor's instructions, including checking whether there is inflammation in the leucorrhea and whether pregnant through urine test, etc. The doctor also needs to instruct the examinee to prohibit sexual intercourse and vaginal medication before the angiography examination, and select the examination date within three to eight days after the end of the examinee's menstruation.

[0061] S2 includes the following steps:

[0062] S21. Thirty minutes before imaging, intramuscularly inject atropine into the examinee to reduce glandular secretion, empty the bladder, and place the examinee in the lithotomy position with the buttocks raised by about 10 cm to make the examination site close to the ultrasound probe, improving the imaging quality. Then inject an anesthetic to reduce the discomfort of the examinee during imaging.

[0063] The specific operation of injecting the contrast agent through the catheter is as follows. The catheter is designed with two water injection ports and one water outlet. One of the water injection ports is connected to the balloon through a guide wire, and normal saline can be injected through this water injection port to inflate the balloon to seal the cervix and prevent the contrast agent from leaking during subsequent contrast imaging. The other water injection port is directly connected to the water outlet and is responsible for sending the contrast agent into the uterine fallopian tubes to achieve subsequent contrast imaging.

[0064] S3 includes the following steps:

[0065] Before using the ultrasound imaging module to image the examinee, first, it is necessary to set the scanning parameters of the ultrasound imaging device, select appropriate frequencies and gains to effectively penetrate tissues and capture blood flow information.

[0066] Start the ultrasound imaging device and perform a routine scan of the uterine fallopian tubes. The probe position can be moved arbitrarily to obtain the best imaging section of the uterine fallopian tubes for imaging. The ultrasound module will display the structural information inside the uterine fallopian tubes. By analyzing the echo signals and using the Doppler effect, information such as blood flow velocity and direction can be obtained.

[0067] S4 includes the following steps:

[0068] S41. Start the photoacoustic imaging device and set appropriate parameters to perform contrast imaging on the uterine fallopian tubes. The main excitation wavelength of ICG in aqueous solution is about 780 nm. After binding to proteins in the blood environment, the absorption peak may redshift to 800 nm. Therefore, select 780 - 800 nm as the excitation wavelength range to obtain the best photoacoustic signal and improve the imaging quality of the uterine fallopian tubes.

[0069] S42. Use the dual - wavelength imaging method to measure the blood oxygen information of the uterine fallopian tubes. Image the uterine fallopian tubes after injecting the contrast agent at the same section by switching two wavelengths, and the blood oxygen value of the uterine fallopian tubes can be obtained through calculation.

[0070] S43. Method for measuring blood oxygen information using dual wavelengths: Hemoglobin in blood is divided into oxyhemoglobin and deoxyhemoglobin, and their light absorption characteristics are different at different wavelengths. By measuring the light absorption of tissue at different wavelengths and the intensity changes of photoacoustic signals, the relative contents of oxyhemoglobin and deoxyhemoglobin can be calculated. Combining these content ratios, the blood oxygen saturation (i.e., the percentage of oxyhemoglobin in blood) can be further calculated. The calculation formula is as follows:

[0071]

[0072] where C Hbo2 and C Hb represent the relative content ratios of oxyhemoglobin Hbo2 and deoxyhemoglobin Hb respectively, and represent the extinction coefficients of oxyhemoglobin Hbo2 and deoxyhemoglobin Hb at wavelengths and respectively, and represent the photoacoustic signal intensities obtained at wavelengths and respectively.

[0073] Figure 2 Figure is a schematic diagram of a catheter for injecting a contrast agent from the vagina into the fallopian tubes. The vaginal catheter is used to achieve two purposes: injecting the contrast agent and preventing the contrast agent from flowing out. The components include: 1. Water injection port 1, 2. Water injection port 2, 3. Guide wire, 4. Outlet, 5. Balloon. The specific operation is as follows: First, insert the vaginal catheter from the vagina into the cervix. The vaginal catheter has two water injection ports. Water injection port 2 is connected to the balloon 5 through the guide wire 3. Inject a certain amount of normal saline through water injection port 2 to inflate the balloon 5 to seal the cervical os and prevent the contrast agent from leaking during subsequent contrast imaging. When performing contrast imaging, inject the ICG contrast agent through water injection port 1. The ICG contrast agent will enter the fallopian tubes through the outlet. As a contrast agent with good biocompatibility, ICG has been approved by the FDA for use as a photoacoustic contrast agent in clinical practice. ICG has a strong absorption ability in the near-infrared band. When ICG enters the fallopian tubes, the light emitted by the laser emission unit can be absorbed by ICG and enhance the photoacoustic signal, which can significantly improve the imaging contrast of the fallopian tubes. This not only helps to improve the imaging accuracy but also better shows the tissue function state of the fallopian tubes.

[0074] Figure 3It is a schematic diagram of the components of a planar array non-radiative photoacoustic and ultrasonic dual-modal imaging device for the uterus and fallopian tubes. The components include: examination bed 1, ultrasonic transducer 2, telescopic shaft 3, robotic arm 4, water bag 5, laser coupling optical path 6, conversion head 7, display screen 8, operation console 9, computer mainframe, and laser emitter encapsulated as one unit 10. Thirty minutes before imaging, atropine is injected intramuscularly into the examinee to reduce glandular secretion. After emptying the bladder, first let the examinee lie flat on the examination bed 1, place the examinee in a suitable position (such as the lithotomy position) and perform anesthesia. The examination bed 1 allows the examinee to adjust to a suitable position on the examination bed 1 according to the requirements of the ultrasonic section, and has the functions of lifting and left-right translation, facilitating the examinee to move up, down, left, and right. After placing the examinee in a suitable position, the positions and heights of the transducer probe 2 can be jointly adjusted by using the three devices of the telescopic shaft 3, robotic arm 4, and conversion head 7 on the ultrasonic transducer 2, so that the water bag 5 under the ultrasonic transducer can fit the scanned target site. The water bag 5 acts as a couplant between the body and the transducer probe, reducing the attenuation of ultrasonic signals during propagation. After placing the appropriate position and placing the ultrasonic transducer probe 2 and the water bag 5 close to the scanned site, the operator can select the ultrasonic mode on the operation console 9. After setting the appropriate scanning parameters and pressing start imaging, the ultrasonic transducer 2 will be responsible for transmitting and receiving ultrasonic signals. The received signals will be transmitted to the computer mainframe 10 for processing and reconstructed into ultrasonic images. The reconstructed images will be displayed in real time on the display screen 8 for the operator to observe. The operator can make detailed adjustments according to the images on the display screen 8 to select a suitable imaging section. After selecting a suitable section, it can be saved and the tool kit can be selected to measure the blood flow information of the scanned site using principles such as Doppler imaging. Then, while maintaining the same position, select the photoacoustic imaging mode. After selecting the wavelength and energy, start imaging. The laser emitter 10 will emit laser with the corresponding wavelength and energy, and the laser will be emitted through the laser coupling path 6 and irradiated onto the scanned site. After the biological tissue absorbs the laser and expands due to heat, the generated ultrasonic signals will be received by the ultrasonic transducer 2. Similarly, the ultrasonic transducer 2 will transmit the received photoacoustic signals to the computer 10 for processing and reconstruction, and display them in real time on the display screen 8 for the examinee to observe. The examinee injects ICG solution through the vaginal catheter, and records the imaging time of the uterus and bilateral fallopian tubes (starting from the injection of the contrast agent), the adverse reactions of the examinee, and the imaging conditions of the uterus and fallopian tubes, etc. When the injection of the ICG solvent is completed, the operator can choose whether to perform dual-wavelength imaging according to the examination requirements of whether to measure blood oxygen information. If dual-wavelength imaging is required, without changing the placement position, only change the wavelength and energy of the laser, set the corresponding scanning parameters for imaging, and calculate the blood oxygen information of the scanned site according to the image information obtained under the two wavelengths and the principle of dual-wavelength blood oxygen measurement.Benefiting from the fact that the ultrasonic transducer 2 can achieve synchronous operation of 512 ultrasonic channels, the device can quickly generate real-time three-dimensional images of the uterus and fallopian tubes, and the operator can also select whether to generate three-dimensional data according to the imaging requirements.

[0075] The above are only the preferred embodiments of the present invention and are not intended to limit the present invention. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principle of the present invention shall be included within the protection scope of the present invention.

Claims

1. A method for hysterosalpingography, characterized in that Based on an imaging device comprising an ultrasonic transducer array, a laser emission unit, a photoacoustic-ultrasonic dual-modal fusion module, and a computer processing system, the method includes the following steps: S1 Preparation for the examiner: The examination time is selected three to eight days after the end of menstruation. Before the examination, a gynecological examination needs to be completed to confirm the absence of gynecological diseases and acute inflammation; S2 Preparation before imaging: Disinfect the vagina of the examiner, empty the bladder, place the examiner in the lithotomy position and anesthetize, insert a catheter and inject saline to inflate the balloon to seal the cervical os; S3 Ultrasonic imaging: Set ultrasonic imaging parameters, adjust the probe position, and obtain images of the uterine tube structure and blood flow information; S4 Photoacoustic contrast imaging: Switch to the photoacoustic mode, set photoacoustic imaging parameters, inject indocyanine green (ICG) solution, and record the development time, development condition, and blood oxygen information; S5 Image fusion: Superimpose the ultrasonic image and the photoacoustic image to synchronously display the uterine tube structure, blood flow, and blood oxygen information.

2. The method according to claim 1, wherein In step S1, the gynecological examination includes inflammation detection and pregnancy testing, and sexual intercourse and vaginal medication are prohibited three days before the examination.

3. The method according to claim 1, characterized in that, In step S2, 30 minutes before imaging, intramuscular injection of atropine is given to the examiner to reduce glandular secretion. After emptying the bladder, place the examiner in the lithotomy position and raise the buttocks by 10 cm to optimize the imaging angle. After anesthesia, inject saline through the catheter to inflate the balloon to seal the cervical os.

4. The method according to claim 1, wherein In step S3, select the ultrasonic imaging mode, use the ultrasonic module to image the uterine tubes in the coronal plane and sagittal plane, and obtain ultrasonic image information, specifically including: Before using the ultrasonic imaging module to image the examiner, first set the imaging parameters of the ultrasonic imaging device, set the frequency to 30 - 40 MHz, so that the ultrasonic probe can effectively penetrate the tissue and capture structural information; Start the ultrasonic imaging device, perform a routine scan of the uterine tubes, and obtain coronal and sagittal plane images of the uterine tubes by moving the probe position; The ultrasonic module will display the structural information inside the uterine tubes. By analyzing the echo signal and using the Doppler effect, the blood flow velocity and direction information of the uterine tube region can be obtained.

5. The method according to claim 1, characterized in that, In step S4, switch to the photoacoustic imaging module and perform photoacoustic contrast imaging to obtain photoacoustic image information and record the development condition of the uterine tubes. The detailed steps specifically include: (1) Start the photoacoustic imaging device, set photoacoustic imaging parameters, and select 780–800 nm as the excitation wavelength to match the maximum absorption peak of ICG; (2) Inject the prepared ICG solution through the catheter; (3) Record the development condition and development time of the uterus and bilateral fallopian tubes; (4) Use the dual-wavelength imaging method to measure the blood oxygen information of the uterine tubes. Image the uterine tubes after injecting the contrast agent at the same section with two different wavelengths, and calculate the blood oxygen data of the uterine tubes by combining the light absorption conditions and the changes in photoacoustic intensity signals at the two wavelengths.

6. The method according to claim 5, wherein The specific principle of measuring the blood oxygen information of the uterine tubes using the dual-wavelength imaging method is as follows: By measuring the light absorption of tissues in the scanned area at different wavelengths and the intensity changes of photoacoustic signals, the relative contents of oxyhemoglobin and deoxyhemoglobin can be calculated. Combining the calculated ratio of the relative contents of oxyhemoglobin and deoxyhemoglobin, the blood oxygen saturation (i.e., the percentage of oxyhemoglobin in the blood) can be further calculated. The calculation formula is as follows: where C Hbo2 and C Hb represent the relative content ratios of oxyhemoglobin Hbo2 and deoxyhemoglobin Hb, respectively, and represent the extinction coefficients of oxyhemoglobin Hbo2 and deoxyhemoglobin Hb at wavelengths and respectively, and represent the photoacoustic signal intensities obtained at wavelengths and respectively.

7. A hysterosalpingography imaging device, characterized in that, The device is applied to hysterosalpingography imaging examination. The device includes a planar array ultrasonic transducer array, a laser emission unit, a photoacoustic and ultrasonic dual-modal fusion unit, and a computer processing system; Among them, the ultrasonic transducer array contains 512 channels, each channel is composed of a piezoelectric element, supports multi-band switching from 1 to 40 MHz and beamforming technology, and can generate three-dimensional structure images in real time; The laser emission unit is integrated in the probe and supports the emission of pulsed lasers with wavelengths of 680 - 1064 nm; The dual-modal fusion unit is used to superimpose ultrasonic images and photoacoustic images in real time; The computer processing system is used to set parameters, reconstruct images and calculate blood flow and blood oxygen data.

8. As shown in claim 7, characterized in that Each ultrasonic channel of the planar array ultrasonic transducer array supports multi-band operation, and the frequency can be adjusted to 1 - 40 MHz to ensure that the device can select and adjust the frequency according to different tissue characteristics during imaging; At the same time, the signals received by 512 ultrasonic transducer channels are combined using advanced beamforming technology to generate images with high signal-to-noise ratio and high spatial resolution, improving the imaging accuracy and reducing image blurring caused by signal attenuation.

9. As shown in claim 7, characterized in that The laser emission unit is built into the probe and is designed with multiple laser beam emission points to ensure uniform laser irradiation on the target tissue area. By combining beamforming technology, the device can enhance weak photoacoustic signals, enabling the effective detection of signals from low-concentration hemoglobin or other absorbing chromophores, thereby further improving the image quality.

10. As shown in claim 7, characterized in that, The photoacoustic and ultrasonic dual-modal fusion unit superimposes ultrasonic images and photoacoustic images through image processing algorithms to generate a fused image, enabling doctors to simultaneously see structural and functional information in one image.

Images