CN105167807A - Ultrasonic testing method for interior of human body, diagnostic apparatus and transducer - Google Patents

Abstract

The invention discloses an ultrasonic detection method, a diagnostic instrument and a transducer in the human body. The method comprises: passing an ultrasonic transducer in the body with a center frequency of 5 MHz to 100 MHz through an ultrasonic catheter with a diameter of 0.1 mm to 5 mm through the natural orifice of the human body or The minimally invasive incision is sent into the part to be tested in the body; the ultrasonic signal is transmitted and received 360 degrees to the part to be tested in the body; at the same time, the ultrasonic transducer in the body is retracted to obtain a three-dimensional image of the part to be tested. The diagnostic instrument includes: an ultrasound catheter with a diameter of 0.1mm~5mm, an in vivo ultrasound transducer with a center frequency of 5MHz~100MHz is installed at the front end, and the back end is connected with a retraction/driving device; the retraction/driving device is connected with an 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 invention sends the ultrasonic transducer into the body part through the natural orifice of the human body or the minimally invasive opening, which has little trauma to the human body and improves the imaging resolution.

Description

Ultrasonic detection method, diagnostic instrument and transducer in human body

technical field

The invention relates to an in vivo diagnostic instrument, in particular to an ultrasonic detection method in a human body, a diagnostic instrument and a transducer.

Background technique

Ultrasound examination refers to a non-invasive examination method that uses the principle of ultrasound to judge the physical characteristics, shape, structure and function of human soft tissues. Because ultrasound equipment is easy to move, low cost, high imaging resolution, and has no radiation damage to the human body, it has been widely used in medicine.

Due to the particularity of the internal environment and the very narrow path to the lesion to be tested in the body, most of the existing diagnostic instruments using the principle of ultrasound imaging are for in vitro testing. The ultrasonic signals used in in vitro ultrasonic testing have to penetrate The skin, the subcutaneous fat layer, and the interface between human tissues usually work at lower operating frequencies; ultrasonic waves with lower frequencies have longer wavelengths, resulting in lower image resolution.

Contents of the invention

In view of the problems existing in the above-mentioned prior art, the present invention proposes an ultrasonic detection method, a diagnostic instrument and a transducer in the human body, which uses an ultrasonic catheter to transmit the ultrasonic transducer in the body through the natural cavity or minimally invasive opening of the human body to The part to be tested in the body improves the image resolution of the test.

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

The invention provides a method for ultrasonic detection in a human body, which comprises the following steps:

S11: Send an in-vivo ultrasound transducer with a center frequency of 5MHz to 100MHz into the body to be tested through an ultrasound catheter with a diameter of 0.1mm to 5mm through the natural orifice of the human body or a minimally invasive opening;

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

S13: Simultaneously withdraw the ultrasound transducer in the body, so as to obtain cross-sectional information of multiple parts to be measured in the body at different positions on the withdrawal path.

The natural cavity of the human body referred to in the present invention includes: urinary tract, reproductive tract, nasal cavity, external auditory canal, and nasolacrimal duct. A very small wound is opened on the body surface, that is, it enters the body through minimal trauma, and the trauma to the human body is small.

Preferably, the step S12 further includes: focusing the ultrasonic signal to reduce the pointing angle factor of the ultrasonic signal to improve imaging resolution, and at the same time reduce the scattering volume to reduce the scattering of the ultrasonic signal by the part to be measured in the body strength.

The present invention also provides an in vivo ultrasonic diagnostic instrument, which includes:

Ultrasonic catheter, the front end of the ultrasonic catheter is equipped with an internal ultrasonic transducer; the diameter of the ultrasonic catheter is 0.1 mm to 5 mm; the center frequency of the internal ultrasonic transducer is 5 MHz to 100 MHz, and the ultrasonic catheter is used for Sending the ultrasonic transducer in the body into the part to be tested in the body through the natural orifice of the human body or the minimally invasive opening;

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 body of the present invention is a miniature sensor, which can enter the body parts through the natural orifice or minimally invasive opening of the human body. The retraction/driving device first sends the ultrasound catheter to the internal body through the guide wire, and then slowly retracts the ultrasound catheter for ultrasound examination, and then a series of internal cross-sectional images and three-dimensional images can be seen on the display screen of the electronic imaging system. Images can assist clinicians in diagnosing lesions in the body, and the imaging images can also guide doctors to perform surgery or perform biopsy.

In the present invention, the ultrasonic transducer is sent into the body through the natural orifice of the human body or a minimally invasive opening, which shortens the detection distance and reduces the scattering intensity of the imaging environment in the body; the higher the frequency, the greater the attenuation per unit distance, in order to ensure the strength of the signal , the frequency is inversely proportional to the imaging distance; therefore, after the detection distance is shortened, the working frequency can be increased, thereby improving the resolution of the ultrasonic in vivo detection image and making clinical detection more accurate.

Preferably, the in vivo ultrasonic transducer is a single-beam ultrasonic transducer or a cylindrical array ultrasonic transducer;

When the ultrasound transducer in the body is a single-beam ultrasound transducer, the ultrasound transducer in the body rotates 360 degrees under the action of the ultrasound catheter;

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

There are mainly two designs of the ultrasonic catheter in the present invention: 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 cross-section in the body, and obtains a cross-sectional image in the body 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, and the electronic delay excitation method is used to collect the sound waves reflected from the cross-section in the body, and the cross-sectional image in the body is obtained after image processing.

There are two types of transducers corresponding to these two designs, namely: (1) single-beam single-element planar transducer (as shown in Figure 1), single-beam single-array surface transducer ( (as shown in Figures 4 and 5); (2) single-beam multi-element annular transducers (as shown in Figures 6, 7 and 8), and cylindrical array transducers (as shown in Figure 2).

Preferably, the in vivo ultrasonic transducer is an in vivo ultrasonic focusing transducer, which can be provided with a focusing function by improving the structure of the ultrasonic transducer itself, or adding a focusing unit at the front end of the ultrasonic transducer.

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 the scattering volume element, defined as 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 body 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 reduced, and the scattering intensity of the internal environment is further reduced, thereby improving the signal-to-noise ratio (signal-scattering-noise ratio) of imaging detection and improving the definition of imaging, namely Image quality.

The realization of the focused ultrasound technology of the present invention 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 in vivo ultrasound transducer 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 in vivo ultrasound transducer 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 in vivo ultrasonic focusing transducer includes a plurality of ultrasonic transducing units and a plurality of 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: $T_i=\frac{{\mathrm{\&Delta;R}}_i}{c}=\frac{f}{c}\&lsqb;\sqrt{1+{\left(\frac{{\mathrm{D.}}_i}{f}\right)}^2}-1\&rsqb;,$ 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 present invention also provides an in vivo ultrasonic transducer, which includes: an ultrasonic transducer unit; which 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 5 MHz to 100 MHz;

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 present invention has the following advantages:

(1) The ultrasonic detection method, diagnostic instrument and transducer in a human body provided by the present invention send the ultrasonic transducer into the body through the natural orifice or minimally invasive opening of the human body, so that the trauma to the human body is relatively small, and at the same time the The distance between the ultrasonic transducer and the body is reduced, and the operating frequency can be increased. Therefore, the resolution is improved, thereby effectively improving the resolution of ultrasound in vivo detection images and the accuracy of clinical detection;

(2) The ultrasonic detection method, diagnostic instrument and transducer in the human body of the present invention, the ultrasonic transducer is penetrated into the inside of human tissue, because the penetration rate of ultrasonic imaging is relatively strong, so not only the surface inside the tissue can be observed, It can also observe the deep lesion;

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

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

Description of drawings

Embodiments of the present invention will be further described below in conjunction with accompanying drawings:

Fig. 1 is the schematic diagram of the ultrasonic transducer in the body of the embodiment 1 of the present invention;

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;

4 is a schematic diagram of an in vivo ultrasonic focusing transducer according to Embodiment 2 of the present invention;

5 is a schematic diagram of an in vivo ultrasonic focusing transducer according to Embodiment 3 of the present invention;

6 is a schematic diagram of an in vivo ultrasonic focusing transducer according to Embodiment 4 of the present invention;

Fig. 7 is a left view of the in vivo ultrasonic focusing transducers arranged in concentric rings according to Embodiment 4 of the present invention;

Fig. 8 is a left view of the in vivo ultrasonic focusing transducers arranged in concentric square rings according to Embodiment 4 of the present invention;

Fig. 9 is a left view of the in-vivo ultrasound focusing transducers arranged in an array according to Embodiment 4 of the present invention;

Fig. 10 is a schematic diagram of the ultrasonic diagnostic instrument in the human body of the present invention;

FIG. 11 is a flow chart of the ultrasonic detection method in the human body of the present invention.

Explanation of symbols: 1-ultrasound catheter, 2-retraction/driving device, 3-electronic imaging system;

11 - In vivo ultrasound transducer;

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

Detailed ways

The embodiments of the present invention are described in detail below. This embodiment is implemented on the premise of the technical solution of the present invention, and detailed implementation methods and specific operating procedures are provided, but the protection scope of the present invention is not limited to the following implementation example.

The ultrasonic transducer in the body of the present invention 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 2 mm to 3 mm; It is used to convert electrical signals into ultrasonic signals and transmit them, and is also used to convert received ultrasonic signals into electrical signals.

Example 1: In Vivo Ultrasound Transducer Using Single Beam Technology

With reference to FIG. 1 , this embodiment describes in detail an in vivo ultrasonic transducer using single beam technology, which includes an ultrasonic 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 in vivo ultrasonic transducer may also be a cylindrical array ultrasonic transducer, which includes a plurality of ultrasonic transducer units distributed along a 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 body of this embodiment can enter the body parts through the natural cavity or minimally invasive opening of the human body through the ultrasonic catheter, which reduces the detection distance and can increase the working frequency to 5MHz-100MHz, thereby improving the lateral and axial resolution. , which improves the resolution of imaging and is helpful for clinical detection.

In order to further improve the imaging clarity, the in vivo ultrasound transducer can be set as an in vivo 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: In vivo ultrasonic focusing transducer using integral acoustic structure focusing technology

As shown in Figure 4, it is a schematic diagram of the in vivo 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 layer Both 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.

Example 3: In vivo ultrasonic focusing transducer using acoustic lens focusing technology

As shown in Figure 5, it is a schematic diagram of the in vivo 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 has For mechanical curved surfaces, the 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: In Vivo Ultrasound Focusing Transducer Using Electronic Focusing Technology

FIG. 6 is a schematic diagram of the in vivo ultrasonic focusing transducer of this embodiment, which includes a plurality of ultrasonic transducing units and a plurality of delay circuits T, each ultrasonic transducing 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:

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

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 body can be PMUT or CMUT.

Embodiment 5: In vivo ultrasonic diagnostic instrument

As shown in FIG. 10 , it is a schematic structural diagram of the in vivo ultrasonic diagnostic instrument of this embodiment, which includes an ultrasonic catheter 1, a withdrawal/driving device 2, and an electronic imaging system 3. The front end of the ultrasonic catheter 1 is equipped with an in vivo ultrasonic transducer. The back end is connected to the retraction/driving device 2, and 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 cross-sectional images and three-dimensional images in the body according to the received ultrasound signals. Therefore, the internal lesion can be judged according to the image. Wherein: the ultrasonic transducer in the body is the ultrasonic transducer in the body as described in any one of embodiments 1-4, where the aperture of the ultrasonic transducer is on the order of millimeters and can be entered through the natural orifice or minimally invasive opening of the human body. body parts.

The natural orifices of the human body include: urinary tract, reproductive tract, nasal cavity, external auditory canal and nasolacrimal duct, etc. Through different natural orifices of the human body, different internal tissues can be observed. Go to the prostate to check the lesions of the part to be tested and obtain a cross-sectional image of the prostate; it can also be sent to the bladder through the urethra to check the lesions of the to-be-tested part of the bladder; The ultrasonic diagnostic instrument is sent into the lesion to be detected in the fallopian tube to obtain a cross-sectional image of the fallopian tube.

Embodiment 6:

As shown in Figure 11, it is a flow chart of the ultrasonic detection method in the human body of this embodiment, which includes the following steps:

S11: Send an in-vivo ultrasound transducer with a center frequency of 5MHz to 100MHz into the body to be tested through an ultrasound catheter with a diameter of 0.1mm to 5mm through the natural orifice of the human body or a minimally invasive opening;

S12: Transmitting and receiving ultrasonic signals at 360 degrees to the part to be tested in the body to obtain cross-sectional information of the part to be tested in the body;

S13: Simultaneously retract the ultrasound transducer in the body to obtain cross-sectional information of multiple parts to be measured in the body at different positions on the retraction path.

In a preferred embodiment, step S12 further includes: focusing the transmitted ultrasonic signal to reduce the pointing angle factor of the ultrasonic signal to improve imaging resolution, and at the same time reduce the scattering volume to reduce the scattering of the ultrasonic signal by the part to be measured in the body Intensity, further improve the imaging resolution, and increase the ultrasonic detection range.

What is disclosed here are only preferred embodiments of the present invention. The purpose of selecting and describing these embodiments in this description is to better explain the principle and practical application of the present invention, not to limit the present invention. 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 invention.

Claims (16)

1. the supersonic detection method in body, is characterized in that, comprises the following steps:

S11: by frequency be 5MHz ~ 100MHz body in ultrasonic transducer be that the ultrasound catheter of 0.1mm ~ 5mm sends into detected part in body through human body natural's tract or Wicresoft mouth by diameter;

S12: detected part 360 degree transmitting in described body, reception ultrasonic signal, to know the cross sectional information of detected part in described body;

S13: simultaneously withdraw ultrasonic transducer in body, with know withdraw diverse location place on path multiple described body in the cross sectional information of detected part, thus obtain the 3-D view of detected part.

2. the supersonic detection method in body according to claim 1, it is characterized in that, described step S12 also comprises: focus on described ultrasonic signal, improve imaging resolution with the sensing angle factor reducing ultrasonic signal, reduce scattering volume simultaneously and to reduce in body detected part to the scattering strength of ultrasonic signal.

3. a diasonograph in body, is characterized in that, comprising:

Ultrasound catheter, the front end of described ultrasound catheter is provided with ultrasonic transducer in body, and the diameter of described ultrasound catheter is 0.1mm ~ 5mm; In described body, the mid frequency of ultrasonic transducer is 5MHz ~ 100MHz, and described ultrasound catheter is used for, through human body natural's tract or Wicresoft's mouth, ultrasonic transducer in described body is sent into detected part in body;

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, can obtain the 3-D view of detected part.

4. diasonograph in body according to claim 3, is characterized in that, in described body, ultrasonic transducer is simple beam ultrasonic transducer or column type array ultrasound transducer;

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

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

5. diasonograph in body according to claim 3, is characterized in that, in described body, ultrasonic transducer is ultrasonic focusing energy transducer in body.

6. diasonograph in body according to claim 5, is characterized in that, in described body, 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.

7. diasonograph in body according to claim 5, is characterized in that, in described body, 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.

8. diasonograph in body according to claim 7, is characterized in that, described acoustic lens is plano-convex or planoconcave lens.

9. diasonograph in body according to claim 5, is characterized in that, in described body, 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: ${\mathrm{\&Delta;R}}_i=f\&CenterDot;\&lsqb;\sqrt{1+{\left(\frac{D_i}{f}\right)}^2}-1\&rsqb;,$ Time difference T _ifor: $T_i=\frac{{\mathrm{\&Delta;R}}_i}{c}=\frac{f}{c}\&CenterDot;\&lsqb;\sqrt{1+{\left(\frac{D_i}{f}\right)}^2}-1\&rsqb;,$ Wherein: i=1,2 ..., 5, f is focal length, and c is the velocity of sound.

10. diasonograph in body according to claim 9, is characterized in that, described multiple ultrasonic transduction unit is arrange with one heart or array arrangement.

Diasonograph in 11. bodies according to claim 10, 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.

Ultrasonic transducer in 12. 1 kinds of bodies, 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 5MHz ~ 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 13. bodies according to claim 12, is characterized in that, also comprises focus ultrasonic unit, focuses on for the ultrasonic signal launched described ultrasonic transduction unit.

Ultrasonic transducer in 14. bodies according to claim 13, 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 15. bodies according to claim 13, 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 16. bodies according to claim 13, 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.