CN205006922U - Through uterine oviduct diasonograph and transducer - Google Patents

Abstract

The utility model discloses a transuterine fallopian tube ultrasonic diagnostic instrument and a transducer. The diagnostic instrument comprises: an ultrasonic catheter with a diameter of 0.5 mm to 5 mm, and an ultrasonic transducer in the fallopian tube with a center frequency of 10 MHz to 100 MHz installed at the front end , the back end is connected to the retraction/driving device; the retraction/driving device is connected to the electronic imaging system. The transducer includes: an ultrasonic transducer unit composed of a backing layer, a piezoelectric layer and an acoustic matching layer closely connected in sequence. The utility model of the transuterine fallopian tube ultrasonic diagnostic instrument and transducer sends the ultrasonic transducer into the fallopian tube through the uterus, improves the imaging resolution, has strong penetration rate, and has no blind angle of vision.

Description

Transuterine fallopian tube ultrasonic diagnostic instrument and transducer

technical field

The utility model relates to a fallopian tube diagnostic instrument, in particular to a transuterine fallopian tube ultrasonic diagnostic instrument and a transducer.

Background technique

Blocked fallopian tubes are the leading cause of female infertility, accounting for about 25% to 35%. The fallopian tube is the channel connecting the ovary and the uterus. It is responsible for the function of fallopian, egg storage, insemination, providing a place for the combination of sperm and egg, and transporting the fertilized egg to the endometrium. If the fallopian tubes are blocked, a series of conception processes such as the combination of sperm and eggs will be hindered, resulting in female infertility. The fallopian tubes are located on both sides of the uterus. There are two openings on each side of the fallopian tubes. The inner end opens in the uterine cavity and connects with the outer corner of the uterine fundus, and the outer end opens in the peritoneal cavity above the ovaries. The entire fallopian tube is a slender and tortuous tubular structure with a total length of about 70-130 mm and a diameter of about 5 mm. The cause of fallopian tube blockage is mainly caused by inflammation. The fallopian tube mucosa undergoes inflammatory changes, and the fallopian tube epithelium degenerates or falls off in pieces, resulting in adhesion of the fallopian tube mucosa, which then blocks the lumen or umbrella of the fallopian tube.

The diagnosis of fallopian tubes is a key step in the treatment of blocked fallopian tubes and the resulting female infertility. At present, the techniques that can be used to diagnose tubal blockage include: laparoscopy, hysteroscopy and salpingoscopy.

A laparoscope is an endoscope that is inserted into the abdominal cavity. During the operation, a small hole is made in the abdomen, and the laparoscopic lens is inserted into the abdominal cavity. The micro-camera at the front end is used to observe the tissues and organs in the pelvic cavity and abdominal cavity, and the overall structure and surrounding tissues of the ovaries and fallopian tubes can be clearly seen. However, this technique cannot observe the structure and lesions inside the fallopian tube, and cannot evaluate the degree and location of fallopian tube blockage.

A hysteroscope is an endoscope that is inserted into the uterus. During the operation, the hysteroscope is inserted into the uterus through the cervix, and the situation in the uterine cavity is observed through the micro camera at the front end. This technology can observe the opening of the fallopian tube in the uterus, but it cannot extend into the fallopian tube to observe the internal structure and blockage of the fallopian tube.

A salpingoscope is an endoscope that is inserted into the fallopian tubes. It is composed of a soft imaging optical fiber, which can be inserted into the fallopian tube to perform optical imaging on the internal structure and obstruction of the entire fallopian tube cavity, but the imaging field of view is small, the imaging resolution is low (millimeter level), and it can only image the tissue surface. Deep tissue lesions cannot be observed.

There are certain shortcomings in the three existing technologies. Laparoscopy and hysteroscopy can only observe from the outside of the fallopian tube. Although the fallopian tube can observe the inside of the fallopian tube, it can only image the tissue surface and cannot observe Deep tissue lesions. Therefore, the current fallopian tube diagnosis technology cannot comprehensively and effectively detect the fallopian tube.

Utility model content

The utility model aims at the problems existing in the above-mentioned prior art, and proposes a transuterine fallopian tube ultrasonic diagnostic instrument and a transducer. Utilizing the principle of ultrasonic imaging, the penetration rate and imaging resolution are improved, and it can not only diagnose the inside of the fallopian tube tissue The surface is imaged, and the detection depth is improved, the observation field of view is large, and there is no blind angle of view.

In order to solve the problems of the technologies described above, the utility model is achieved through the following technical solutions:

The utility model provides a transuterine fallopian tube ultrasonic diagnostic instrument, which comprises:

An ultrasonic catheter, the front end of the ultrasonic catheter is equipped with an intra-fallopian ultrasonic transducer; the diameter of the ultrasonic catheter in the fallopian tube is 0.5 mm to 5 mm; the center frequency of the intra-fallopian ultrasonic transducer is 10 MHz to 100 MHz, and the ultrasonic The catheter is used to send the ultrasound transducer in the fallopian tube to the site to be tested in the fallopian tube through the uterus;

Retraction/driving device;

and electronic imaging systems on which are loaded electronic components for reconstructing images; wherein:

The back end of the ultrasonic catheter is connected with the withdrawal/driving device; the withdrawal/driving device is connected with the electronic imaging system.

The ultrasonic transducer in the fallopian tube of the utility model is a miniature sensor, which can enter the fallopian tube through the uterus (the diameter is generally less than 5mm). The retraction/driving device first sends the ultrasonic catheter to the fallopian tube by the guide wire, then rotates and slowly withdraws the ultrasonic catheter for ultrasonic examination, and a series of cross-sectional images of the fallopian tube can be seen on the display screen of the electronic imaging system And three-dimensional images to assist clinicians in the diagnosis of lesions in the fallopian tubes, and the imaging images can also guide doctors to perform surgery or biopsy.

The utility model sends the ultrasonic transducer through the uterus into the fallopian tube, utilizes the principle of ultrasonic imaging, has high imaging resolution (micron level), improves the picture definition, and has strong penetrating ability, not only can observe the inner surface of the fallopian tube, It can also observe deep tissue lesions, and the penetration depth can reach more than 5 mm; in addition, through 360-degree rotation and withdrawal of the catheter, the obtained two-dimensional image can be converted into a three-dimensional image, and the entire fallopian tube can be reconstructed in three dimensions, so that there is no observation blind spot.

Preferably, the ultrasound transducer in the fallopian tube is a single-beam ultrasound transducer or a cylindrical array ultrasound transducer;

When the ultrasonic transducer in the fallopian tube is a single-beam ultrasonic transducer, the ultrasonic transducer in the fallopian tube rotates 360 degrees under the action of the ultrasonic catheter;

When the ultrasonic transducer in the fallopian tube is a cylindrical array ultrasonic transducer, the ultrasonic transducer in the fallopian tube includes a plurality of ultrasonic transducer units distributed 360 degrees along the cylindrical surface.

There are mainly two designs of the ultrasonic catheter described in the utility model: mechanical rotary type and electronic phased array type. The mechanical rotation type rotates the transducer of a single array element within a range of 360 degrees, emits ultrasonic waves, and collects the sound waves reflected back from the fallopian tube section, and obtains the cross-sectional image of the fallopian tube through image processing. At this time, the retraction device will It also has the function of driving the transducer to rotate. The electronic phased array transducers are arranged in a cylindrical shape without rotation. The electronic delayed excitation method is used to collect the sound waves reflected from the section of the fallopian tube, and the cross-sectional image of the fallopian tube is obtained after image processing.

There are two kinds of transducers corresponding to these two designs, namely: (1) single-beam single-element planar transducer, single-beam single-array surface transducer (as shown in Figure 1); (2) Single-beam multi-array element ring transducers (as shown in Figure 6, Figure 7, and Figure 8), and cylindrical array transducers (as shown in Figure 2).

Preferably, the ultrasonic transducer in the fallopian tube is an ultrasonic focusing transducer in the fallopian tube, which can have a focusing function by improving the structure of the ultrasonic transducer itself, or can add a focusing function at the front end of the ultrasonic transducer. unit.

The sound intensity of medical ultrasonic testing is defined as the sound energy per unit area, which is equal to the ratio of the total energy W to the beam area:

$\mathrm{<span\; class="notranslate">\; I</span>}<span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; W</span>}}{\mathrm{<span\; class="notranslate">\; S</span>}}$

Obviously, for a given sound power, reducing the beam area S can increase the sound intensity I, thereby improving the signal-to-noise ratio of imaging detection.

For a given spatial angle dΩ, the intensity of ultrasonic scattered sound is Volume integral over space. where Sv is the volume scattering coefficient. dv is a scattering volume element, defined as dv=12r ² dΩ*cτ, where: r is the distance from the ultrasonic transducer to the target, c is the speed of sound, and τ is the pulse length; and are the pointing angle factors of transmitting and receiving respectively, the principle of which is shown in Figure 3.

It is not difficult to see that reducing the pointing angle factor and It will directly improve the resolution of imaging detection. When the ultrasound transducer in the fallopian tube has a focusing function, not only the pointing angle factor is reduced and The resolution of imaging detection is improved; at the same time, the scattering volume dv is also reduced, and the scattering intensity of the environment in the fallopian tube is further reduced, thereby improving the signal-to-noise ratio (signal scattering-to-noise ratio) of imaging detection and improving the definition of imaging. That is, the quality of the image.

The realization of the focused ultrasonic technology of the utility model can be divided into: (1) mechanical structure focusing; (2) electronic focusing. Mechanical structure focusing can be further divided into overall acoustic structure focusing and acoustic lens focusing.

Preferably, the ultrasound transducer in the fallopian tube includes a backing layer, a piezoelectric layer and an acoustic matching layer that are closely connected in sequence; wherein:

The backing layer and/or the piezoelectric layer and/or the acoustic matching layer have a mechanical curved surface, which uses the overall acoustic structure focusing technology to achieve focusing, and the curvature radius of the mechanical curved surface is determined according to a predetermined focal length f , the focus factor K is defined as the ratio of the focal length f to the transducer aperture d, namely: K=f/d, and the size of the aperture d can be determined according to a predetermined focus factor K and the focal length f.

Preferably, the ultrasound transducer in the fallopian tube includes a backing layer, a piezoelectric acoustic layer, a matching layer, and an acoustic lens that are closely connected in sequence; wherein:

The acoustic lens has a mechanical curved surface, which is the focus of the acoustic lens, and its radius of curvature is determined according to a predetermined focal length f, and the focusing factor K is defined as the ratio of the focal length f to the transducer aperture d, that is: K=f/d, aperture d The size of can be determined according to the predetermined focus factor K and focal length f.

Preferably, the acoustic lens is a plano-convex or plano-concave lens.

Preferably, the intrafallopian tube ultrasonic focusing transducer includes multiple ultrasonic transducer units and multiple delay circuits, which are electronic focusing; wherein:

Each of the ultrasonic transducer units is connected with a delay circuit to compensate the time difference caused by the sound path difference of the sound wave from the focal point to each ultrasonic transducer unit, and the sound path difference and the time difference are determined according to a predetermined center distance difference ; The distance from the i-th ultrasonic transducer unit to the central axis is D _i , and the sound path difference introduced by the center distance difference D _i is: ${\mathrm{\&Delta;R}}_i=f\&Center\; Dot;\&lsqb;\sqrt{1+{\left(\frac{{\mathrm{D.}}_i}{f}\right)}^2}-1\&rsqb;,$ The time difference T _i is: $T_i=\frac{{\mathrm{\&Delta;R}}_i}{c}=\frac{f}{c}\&Center\; Dot;\&lsqb;\sqrt{1+{\left(\frac{{\mathrm{D.}}_i}{f}\right)}^2}-1\&rsqb;,$ Among them: i=1,2...,5, f is the focal length, c is the speed of sound.

Preferably, the plurality of ultrasonic transducing units are arranged concentrically or in an array.

Preferably, when the plurality of ultrasonic transducer units are arranged concentrically, they are arranged in concentric circular rings or concentric square rings.

The utility model also provides an ultrasonic transducer in the fallopian tube, which includes: an ultrasonic transducer unit; it includes a backing layer, a piezoelectric layer and an acoustic matching layer that are closely connected in sequence; wherein:

The center frequency of the ultrasonic transducer unit is 10MHz to 100MHz;

The ultrasonic transducer unit is used to convert electrical signals into ultrasonic signals and transmit them, and is also used to convert received ultrasonic signals into electrical signals.

Preferably, an ultrasonic focusing unit is also included, configured to focus the ultrasonic signal emitted by the ultrasonic transducing unit.

Preferably, the focusing unit is specifically a mechanical curved surface formed on the backing layer, the piezoelectric layer and the acoustic matching layer.

Preferably, the focusing unit is specifically an acoustic lens with a mechanically curved surface, and the acoustic lens is closely connected to the acoustic matching layer of the ultrasonic transducer unit.

Preferably, the ultrasonic transducer unit includes a plurality of;

The focusing unit is specifically a plurality of delay circuits, each of the ultrasonic transducing units is connected to one of the delay circuits.

Compared with the prior art, the utility model has the following advantages:

(1) The utility model provides a transuterine fallopian tube ultrasonic diagnostic instrument and transducer. The ultrasonic transducer is sent into the fallopian tube through the uterus, and the ultrasonic detection catheter is transported through the uterus. A small incision in the abdomen is a completely non-invasive diagnostic method;

(2) The transuterine fallopian tube ultrasonic diagnostic instrument and transducer of the present utility model can image the cross-section of the fallopian tube by utilizing the principle of ultrasonic imaging, and the imaging depth of the cross-section can reach more than 5 millimeters, and the resolution can be Up to 100 microns, able to observe deep lesions in fallopian tube tissue;

(3) The transuterine fallopian tube ultrasonic diagnostic instrument and transducer of the present utility model can convert the two-dimensional image into a three-dimensional image through the retraction of the catheter, carry out three-dimensional reconstruction of the entire fallopian tube, expand the observation field of view, and there is no field of view blind spot;

(4) When the transuterine fallopian tube ultrasonic transducer of the present invention has a focusing function, it can further reduce the scattering intensity of the environment in the fallopian tube, further improve the signal-to-noise ratio of imaging detection, thereby improving the definition of imaging.

Of course, any product implementing the present utility model does not necessarily need to achieve all the above-mentioned advantages at the same time.

Description of drawings

Below in conjunction with accompanying drawing, the embodiment of the present utility model is further described:

Fig. 1 is the schematic diagram of the ultrasonic transducer in fallopian tube of embodiment 1 of the present utility model;

Fig. 2 is the schematic diagram of cylindrical array transducer;

Fig. 3 is the schematic diagram of the volume scattering coefficient and the scattered sound intensity of the ultrasonic transducer;

Fig. 4 is the schematic diagram of the ultrasonic focusing transducer in the fallopian tube of embodiment 2 of the present utility model;

Fig. 5 is the schematic diagram of the ultrasonic focusing transducer in the fallopian tube of embodiment 3 of the present utility model;

Fig. 6 is the schematic diagram of the ultrasonic focusing transducer in the fallopian tube of embodiment 4 of the present utility model;

Fig. 7 is the left side view that the ultrasonic focusing transducers in the fallopian tube of embodiment 4 of the present invention are arranged in concentric rings;

Fig. 8 is the left side view that the ultrasonic focusing transducers in the fallopian tube of embodiment 4 of the present invention are arranged in concentric square rings;

Fig. 9 is a left view of the ultrasound focusing transducers arranged in an array in the fallopian tube according to Embodiment 4 of the present utility model;

Fig. 10 is a schematic diagram of a transuterine fallopian tube ultrasonic diagnostic instrument of the present invention;

Fig. 11 is a schematic diagram of detection by the transuterine fallopian tube ultrasonic diagnostic instrument of the present invention.

Explanation of symbols: 1-ultrasound catheter, 2-retraction/driving device, 3-electronic imaging system, 4-vagina, 5-uterus, 6-fallopian tube;

11-Intra-fallopian tube ultrasound transducer;

111-backing layer, 112-piezoelectric layer, 113-acoustic matching layer, 114-lens.

detailed description

The following is a detailed description of the embodiments of the present utility model. This embodiment is implemented on the premise of the technical solution of the present utility model, and detailed implementation methods and specific operating procedures are provided, but the protection scope of the present utility model is not limited to the following the described embodiment.

The ultrasonic transducer in the fallopian tube of the present utility model includes: an ultrasonic transducer unit, which includes a backing layer, a piezoelectric layer and an acoustic matching layer closely connected in sequence, and the aperture of the ultrasonic transducer is 0.3 mm to 3 mm; The energy unit is used to convert the electrical signal into an ultrasonic signal and transmit it, and is also used to convert the received ultrasonic signal into an electrical signal.

Example 1: Intrafallopian Tube Ultrasound Transducer Using Single Beam Technology

With reference to FIG. 1 , this embodiment describes in detail the intrafallopian ultrasound transducer using single-beam technology, which includes an ultrasound transducer unit composed of a backing layer 111 , a piezoelectric layer 112 and an acoustic matching layer 113 that are closely connected in sequence. Correspondingly, the ultrasonic catheter driving its movement drives its 360-degree rotation.

In different embodiments, the ultrasound transducer in the fallopian tube may also be a cylindrical array ultrasound transducer, which includes a plurality of ultrasound transducer units distributed along the cylindrical surface for 360 degrees, as shown in FIG. 2 . Correspondingly, the moving ultrasonic catheter only needs to be driven to move back and forth, and does not need to be rotated.

The ultrasonic transducer in the fallopian tube of this embodiment can enter the fallopian tube through the uterus through the ultrasonic catheter, which reduces the detection distance and increases the working frequency to 10MHz-100MHz, thereby improving the lateral and axial resolution and improving the imaging resolution. rate, which is helpful for clinical detection.

In order to further improve the imaging clarity, the intrafallopian tube ultrasound transducer can be set as an intrafallopian tube ultrasound focusing transducer, which can reduce the pointing angle factor and Further directly improve the resolution of imaging detection; on the original basis, it also includes a focusing unit, which is used to focus the ultrasonic signal emitted by the ultrasonic transducer unit, which can be achieved in the following two ways: ( 1) Mechanical structure focusing; (2) Electronic focusing. Mechanical structure focusing can be further divided into overall acoustic structure focusing and acoustic lens focusing. This will be described below in conjunction with specific embodiments.

Example 2: Ultrasound Focusing Transducer in the Fallopian Tube Using Whole Acoustic Structure Focusing Technology

As shown in Figure 4, it is a schematic diagram of the intrafallopian tube ultrasonic focusing transducer of this embodiment, which includes a backing layer 111, a piezoelectric layer 112 and an acoustic matching layer 113 closely connected in sequence, wherein: the backing layer 111, the piezoelectric Both the layer 112 and the acoustic matching layer 113 have mechanical curved surfaces, and the radii of curvature of the three can be calculated and set according to the requirements of the focused sound field. The focus factor K is defined as the ratio of the focal length f to the transducer aperture d, ie: K=f/d. Given the focus factor K and the focal length f, the size of the aperture d can be calculated.

Embodiment 3: Intrafallopian tube ultrasonic focusing transducer using acoustic lens focusing technology

As shown in Figure 5, it is a schematic diagram of the intrafallopian tube ultrasonic focusing transducer of this embodiment, which includes a backing layer 111, a piezoelectric layer 112, an acoustic matching layer 113, and an acoustic lens 114 closely connected in sequence, wherein the acoustic lens 4 It has a mechanical curved surface, and its radius of curvature can be calculated and set according to the requirements of the focused sound field.

The acoustic lens 114 can be a plano-convex lens or a plano-concave lens, which is determined according to the sound velocity of the lens material. For the lens material whose sound velocity is lower than the sound velocity of the medium, it is a plano-convex lens, as shown by the dotted line in Figure 6; for the lens material whose sound velocity is higher than the medium sound velocity, it is a plano-concave lens, as shown by the solid line in Figure 6.

Example 4: Ultrasound Focusing Transducer Using Electronic Focusing Technology in the Fallopian Tube

As shown in Figure 6, it is a schematic diagram of the intrafallopian tube ultrasonic focusing transducer of this embodiment, which includes a plurality of ultrasonic transducer units and a plurality of delay circuits T, and each ultrasonic transducer unit corresponds to a delay circuit T,

In this embodiment, five concentric square ring transducing units are taken as an example. The left views are shown in Figure 7, which are respectively marked as e1,...e5, and the time for sound waves to reach each ultrasonic transducing unit from point F in the free sound field is different. of. Therefore, the total received signal is the superposition of signals of different phases, and the output signal cannot be the maximum. The output terminal of each ultrasonic transducer unit is connected with a delay circuit to compensate the time difference caused by the sound path difference of the sound wave from point F to each ultrasonic transducer unit. The distance from the i-th ultrasonic transducer unit to the central axis is D _i , then the sound path difference introduced by the center distance difference D _i is:

${\mathrm{<span\; class="notranslate">\; \&Delta;R</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; f</span>}<span\; class="notranslate">\; \&Center\; Dot;</span><span\; class="notranslate">\; \&lsqb;</span>\sqrt{\mathrm{<span\; class="notranslate">\; 1</span>}<span\; class="notranslate">\; +</span>{<span\; class="notranslate">\; (</span>\frac{{\mathrm{<span\; class="notranslate">\; D.</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}}{\mathrm{<span\; class="notranslate">\; f</span>}}<span\; class="notranslate">\; )</span>}^{\mathrm{<span\; class="notranslate">\; 2</span>}}}<span\; class="notranslate">\; -</span>\mathrm{<span\; class="notranslate">\; 1</span>}<span\; class="notranslate">\; \&rsqb;</span>$

The time difference T _i is:

${\mathrm{<span\; class="notranslate">\; T</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; =</span>\frac{{\mathrm{<span\; class="notranslate">\; \&Delta;R</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}}{\mathrm{<span\; class="notranslate">\; c</span>}}<span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; f</span>}}{\mathrm{<span\; class="notranslate">\; c</span>}}<span\; class="notranslate">\; \&Center\; Dot;</span>\sqrt{\mathrm{<span\; class="notranslate">\; 1</span>}<span\; class="notranslate">\; +</span>{<span\; class="notranslate">\; (</span>\frac{{\mathrm{<span\; class="notranslate">\; D.</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}}{\mathrm{<span\; class="notranslate">\; f</span>}}<span\; class="notranslate">\; )</span>}^{\mathrm{<span\; class="notranslate">\; 2</span>}}}<span\; class="notranslate">\; -</span>\mathrm{<span\; class="notranslate">\; 1</span>}<span\; class="notranslate">\; \&rsqb;</span>$

In the formula, i=1,2...,5, f is the focal length, and c is the speed of sound. When D _i is given, by adjusting the time difference T _i of the delay circuit, the focal length f can be adjusted to achieve variable focal length ultrasound focusing.

In different embodiments, multiple ultrasonic transducer units can also be arranged in concentric square rings, as shown in FIG. 8 in the left view; they can also be arranged in an array, as shown in FIG. 9 in the left view. In the above-mentioned embodiment, the material of the piezoelectric layer 112 can be a piezoelectric ceramic material, a piezoelectric thick film material, a piezoelectric thin film material, a piezoelectric ceramic composite material or a piezoelectric single crystal composite material; the ultrasonic focusing transducer in the oviduct can be be PMUT or CMUT.

Embodiment 5: fallopian tube ultrasonic diagnostic instrument

As shown in Figure 10, it is the structure schematic diagram of the fallopian tube ultrasonic diagnostic instrument of the present embodiment, and it comprises ultrasonic catheter 1, withdrawal/driving device 2 and electronic imaging system 3, and the front end of ultrasonic catheter 1 is equipped with ultrasonic transducer in fallopian tube , the back end is connected to the retraction/driving device 2, the retraction/driving device 2 is connected to the electronic imaging system 3, the electronic imaging system 3 is loaded with electronic components for reconstructing images, and reconstructs the cross-sectional image and three-dimensional image of the fallopian tube according to the received ultrasonic signal , so as to judge the fallopian tube lesion according to the image. Wherein: the ultrasonic transducer in the fallopian tube is the ultrasonic transducer in the fallopian tube as described in any one of embodiments 1-4, where the aperture of the ultrasonic transducer is on the order of millimeters, between 0.3mm and 3mm, and can be Through the uterus into the fallopian tubes.

In this embodiment, the ultrasonic catheter 1 specifically includes: an imaging core, a catheter sheath surrounding the imaging core, and a catheter joint positioned at the rear end of the imaging core. The front end of the imaging core is equipped with an ultrasound transducer in the fallopian tube; The driving device 2 specifically includes: a driving motor for controlling the movement of the ultrasonic catheter 1, a motor driving circuit, and a transmitting and receiving conversion circuit for controlling the transmission and receiving conversion of the ultrasonic transducer, and the catheter connector is connected to the driving motor through a catheter interface device; the electronic imaging system 3 specifically Including: excitation and receiving circuit of ultrasonic transducer, signal and image processing device and user operation interface.

As shown in Figure 11, it is the detection schematic diagram of the transuterine fallopian tube ultrasonic diagnostic instrument of the present embodiment. It rotates, retracts and advances inside the ultrasonic catheter without directly contacting the fallopian tube muscle tissue and causing no damage to the tissue.

The detection method of the fallopian tube ultrasonic diagnostic instrument through the uterus of the present utility model comprises the following steps:

S11: Send an intra-fallopian ultrasound transducer with a center frequency of 10MHz to 100MHz through the uterus through an ultrasound catheter with a diameter of 0.5mm to 5mm to the site to be tested in the fallopian tube;

S12: Transmitting and receiving ultrasonic signals at 360 degrees to the part of the fallopian tube to be tested, so as to obtain the cross-sectional information of the part of the fallopian tube to be tested;

S13: Simultaneously withdrawing the ultrasonic transducer in the fallopian tube, so as to obtain cross-sectional information of multiple parts of the fallopian tube to be measured at different positions on the withdrawing path.

Step S12 may also include: focusing the transmitted ultrasonic signal to reduce the pointing angle factor of the ultrasonic signal to improve the imaging resolution, and at the same time reduce the scattering volume to reduce the scattering intensity of the fallopian tube to the ultrasonic signal to further improve the imaging resolution, and increase the ultrasonic detection range.

What is disclosed here is only the preferred embodiment of the utility model. This specification selects and describes these embodiments in detail to better explain the principle and practical application of the utility model, not to limit the utility model. Any modifications and changes made by those skilled in the art within the scope of the description shall fall within the protection scope of the present utility model.

Claims (14)

1. a transuterine supersonic diagnosis of oviduct instrument, is characterized in that, comprising:

Ultrasound catheter, the front end of described ultrasound catheter is provided with ultrasonic transducer in fallopian tube, and the diameter of described ultrasound catheter is 0.5mm ~ 5mm; In described fallopian tube, the mid frequency of ultrasonic transducer is 10MHz ~ 100MHz, and described ultrasound catheter is used for, through uterus, ultrasonic transducer in described fallopian tube is sent into fallopian tube detected part;

Withdraw/driving device;

And electronic imaging system, it is mounted with the electronic unit rebuilding image; Wherein:

The rear end of described ultrasound catheter withdraws with described/and driving device is connected; Describedly to withdraw/driving device is connected with described electronic imaging system.

2. supersonic diagnosis of oviduct instrument according to claim 1, is characterized in that, in described fallopian tube, ultrasonic transducer is simple beam ultrasonic transducer or column type array ultrasound transducer;

When in described fallopian tube, ultrasonic transducer is simple beam ultrasonic transducer, ultrasonic transducer 360 degree of rotations under the effect of described ultrasound catheter in described fallopian tube;

When in described fallopian tube during ultrasonic transducer column type array ultrasound transducer, in described fallopian tube, ultrasonic transducer comprises the ultrasonic transduction unit of multiple 360 degree of distributions along the face of cylinder.

3. supersonic diagnosis of oviduct instrument according to claim 1, is characterized in that, in described fallopian tube, ultrasonic transducer is ultrasonic focusing energy transducer in fallopian tube.

4. supersonic diagnosis of oviduct instrument according to claim 3, is characterized in that, in described fallopian tube, ultrasonic transducer comprises close-connected backing layer, piezoelectric layer and acoustic matching layer successively; Wherein:

Described backing layer and/or described piezoelectric layer and/or described acoustic matching layer have mechanical curved surface, the radius of curvature of described mechanical curved surface is determined according to predetermined focal distance f, (ionospheric) focussing factor K is defined as the ratio of focal distance f and transducer aperture d, that is: the size of K=f/d, aperture d can be determined according to predetermined (ionospheric) focussing factor K and focal distance f.

5. supersonic diagnosis of oviduct instrument according to claim 3, is characterized in that, in described fallopian tube, ultrasonic transducer comprises close-connected backing layer, piezoelectric layer sound, matching layer and acoustic lens successively; Wherein:

Described acoustic lens has mechanical curved surface, and its radius of curvature is determined according to predetermined focal distance f, and (ionospheric) focussing factor K is defined as the ratio of focal distance f and transducer aperture d, that is: K=f/d, and the size of aperture d can be determined according to predetermined (ionospheric) focussing factor K and focal distance f.

6. supersonic diagnosis of oviduct instrument according to claim 5, is characterized in that, described acoustic lens is plano-convex or planoconcave lens.

7. supersonic diagnosis of oviduct instrument according to claim 3, is characterized in that, in described fallopian tube, ultrasonic focusing energy transducer comprises multiple ultrasonic transduction unit and multiple delay circuit; Wherein:

Each described ultrasonic transduction unit connects a described delay circuit, and in order to compensation sound wave from focus to the time difference caused by the path difference of each ultrasonic transduction unit, path difference and time difference are determined according to predetermined centre-to-centre spacing deviation; I-th ultrasonic transduction unit is D to the distance of central axis _i, by centre-to-centre spacing deviation D _ithe path difference introduced is: time difference T _ifor: wherein: i=1,2 ..., 5, f is focal length, and c is the velocity of sound.

8. supersonic diagnosis of oviduct instrument according to claim 7, is characterized in that, described multiple ultrasonic transduction unit is arrange with one heart or array arrangement.

9. supersonic diagnosis of oviduct instrument according to claim 8, is characterized in that, when described multiple ultrasonic transduction unit is arranged with one heart, it is donut arrangement or Fang Huan arrangement with one heart.

10. a ultrasonic transducer in fallopian tube, is characterized in that, comprising: ultrasonic transduction unit; It comprises close-connected backing layer, piezoelectric layer and acoustic matching layer successively; Wherein:

The mid frequency of described ultrasonic transduction unit is 10MHz ~ 100MHz;

Described ultrasonic transduction unit is used for converting electrical signals to ultrasonic signal and launches, also for the ultrasonic signal received is converted to the signal of telecommunication.

Ultrasonic transducer in 11. fallopian tube according to claim 10, is characterized in that, also comprises focus ultrasonic unit, focuses on for the ultrasonic signal launched described ultrasonic transduction unit.

Ultrasonic transducer in 12. fallopian tube according to claim 11, is characterized in that, described focusing unit is specially the mechanical curved surface formed on described backing layer, described piezoelectric layer and described acoustic matching layer.

Ultrasonic transducer in 13. fallopian tube according to claim 11, is characterized in that, described focusing unit is specially the acoustic lens with mechanical curved surface, the acoustic matching layer compact siro spinning technology of described acoustic lens and described ultrasonic transduction unit.

Ultrasonic transducer in 14. fallopian tube according to claim 11, is characterized in that, described ultrasonic transduction unit comprises multiple;

Described focusing unit is specially multiple delay circuit, and each described ultrasonic transduction unit connects a described delay circuit.