CN217548067U - Elasticity detection device, probe and system - Google Patents
Elasticity detection device, probe and system Download PDFInfo
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- CN217548067U CN217548067U CN202123303665.4U CN202123303665U CN217548067U CN 217548067 U CN217548067 U CN 217548067U CN 202123303665 U CN202123303665 U CN 202123303665U CN 217548067 U CN217548067 U CN 217548067U
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Abstract
The utility model discloses a sound passes through structure, elasticity detection device, probe and system, wherein, sound passes through the structure and passes through the structure body and set up including the sound and be in the bellying at sound transmission structure top. The utility model discloses a sound that will be provided with the bellying passes through the structure setting at ultrasonic transducer's front end to through bellying low-frequency vibration treat the target in producing the shear wave waiting, not only realized image two dimension B image guide function, can also guarantee instantaneous elasticity detection quality.
Description
Technical Field
The utility model relates to the technical field of medical equipment, what especially relate to is a sound passes through structure, elasticity detection device, probe and system.
Background
In clinical practice, the change of the hardness or elasticity of biological tissues is often closely related to the pathological change degree of the tissues, and elastography has important research significance on the early diagnosis of soft tissue pathological changes. The Transient Elastography (TE) is used as a liver disease detection technology, has the characteristics of non-invasiveness, rapidness and quantification, can provide effective tools for early screening, diagnosis and treatment evaluation of liver diseases for people with chronic liver diseases, solves the problems of trauma, inaccuracy and the like of the traditional diagnosis mode, and has wide application prospect. Currently, due to the accuracy of the instant elastography technique in diagnosing the degree of fibrosis, it has been recommended by the global major liver disease guidelines, including the world health organization. But the disadvantage is also obvious, because the single-element probe is usually used for elastic detection, the image guide function is lacked, namely two-dimensional imaging can not be carried out. The single-array-element probe can only realize one-dimensional imaging, cannot directly realize two-dimensional imaging, and needs to realize observation of a two-dimensional imaging area through a mechanical fan scanning mode to realize the two-dimensional imaging, but can increase the system design difficulty and increase the design cost. In conventional transient elastography system designs, mechanical fan-sweeping cannot be achieved due to its own need to participate in mechanical vibrations. Many large blood vessels are distributed in liver tissues, areas and positions where cysts and the like are not suitable for instantaneous elastography exist, the positions need to be avoided during instantaneous elastography detection, and otherwise, the result of elasticity detection is abnormal and even wrong. If an image guide function is introduced into the instantaneous elastography technology, the accuracy of instantaneous elastography detection can be increased, the operation experience of doctors is further improved, and better diagnosis service is provided for clinical patients.
The instantaneous elastography principle is mainly to judge the hardness of the liver by measuring the propagation speed of low-frequency shear waves in liver tissue fibers, so as to evaluate the degree of liver fibrosis. The shear wave in the instantaneous elastic imaging is acted on the surface of a detection target by using the mechanical vibration of a probe, the shear wave is excited in the detection target, and the propagation of the shear wave in the central shaft region under the probe is tracked and detected. When the size of a probe used for exciting shear waves is increased, the excited shear waves have diffraction phenomena to a certain degree, the diffraction phenomena are not beneficial to instantaneous elastic detection, the shear wave speed obtained by utilizing the shear waves to perform elastic detection deviates from a true value, so that the detection result has deviation or errors, and the elastic detection quality is reduced. Therefore, in the conventional transient elastography technology, in order to reduce the size of the probe (ensure the quality of elastography), a single-element probe is generally adopted for elastography. Although the multi-array-element ultrasonic transducer can provide a pattern guide function, the size of the transducer is increased, so that the conventional instantaneous elastography technology has the problem that the image guide function and the elastography quality cannot be compatible.
Accordingly, the prior art is yet to be improved and developed.
SUMMERY OF THE UTILITY MODEL
In view of the above-mentioned prior art not enough, the utility model aims to provide an acoustically transparent structure, elasticity detection device, probe and system to solve the problem that the image guide function and the elasticity detection quality that exist can't be compromise among the current elasticity detection probe.
The technical scheme of the utility model as follows:
an acoustically transparent structure, comprising:
a sound-transmitting structural body;
the bulge is arranged at the top of the sound transmission structure body.
The utility model discloses a further set up, the bellying with the sound passes through the coaxial setting of structure body.
The utility model discloses a further setting, the bellying vibration produces shear wave in the detection object.
The utility model discloses a further setting, the bellying with the integrative setting of sound transmission structure body.
In a further arrangement, the two extension tangent planes on the surface width direction of the convex part are respectively 0-30 degrees with the included angle between the central shafts of the convex part.
In a further aspect of the present invention, the width of the surface of the protrusion is 5-15mm.
In a further aspect of the present invention, the protruding portion is cylindrical or truncated cone-shaped.
The utility model discloses a further setting, the length of the terminal surface of bellying is less than the twice the width of the terminal surface of bellying.
Based on same utility model think, the utility model also provides an elasticity detection device, it includes:
an ultrasonic transducer;
the acoustic transmission structure is arranged at the front end of the ultrasonic transducer.
In a further aspect of the present invention, the ultrasonic transducer is a multi-element ultrasonic transducer.
The utility model discloses a further setting, ultrasonic transducer includes first array and is located the second array of first array both sides, the bellying sets up directly over the first array, the center pin of bellying with the center pin coincidence of first array.
The utility model discloses a further setting, in instantaneous elasticity imaging process, at least part array element of first array is used for launching and receiving ultrasonic signal to trail and detect the shear wave.
The utility model discloses a further setting, the array direction of ultrasonic transducer's array element with the corresponding setting of length direction on the surface of bellying.
The utility model discloses a further setting, the structure is passed through alone to the sound activity or the sound pass through the structure with the integrative activity of ultrasonic transducer.
The utility model discloses a further setting, the sound pass through the structure with during the integrative activity of ultrasonic transducer, ultrasonic transducer with the sound passes through structure lug connection or indirect connection.
The utility model discloses a further setting, the sound pass through the structure with be provided with transition structure between the ultrasonic transducer.
The utility model discloses a further setting, when the structure is passed through to the sound moves about alone, ultrasonic transducer with it is provided with the connecting piece to pass through between the structure to the sound.
The utility model discloses a further setting, ultrasonic transducer with be provided with transition structure between the structure is passed through to the sound.
In a further aspect of the present invention, the connector is an elastic acoustically transparent bag connected between the ultrasound transducer and the acoustically transparent structure; wherein, the elastic sound transmission bag is internally provided with a sound transmission medium.
In a further aspect of the present invention, the acoustically transparent medium is acoustically transparent liquid.
The utility model discloses a further setting, the sound pass through the structure with the coaxial setting of ultrasonic transducer.
The utility model discloses a further setting, elasticity detection device still includes: an installation part; the installation part is arranged at the bottom of the sound transmission structure.
The utility model discloses a further setting, the sound pass through the structure with installation department integrated into one piece.
The utility model discloses a further setting, the installation department with the position that ultrasonic transducer corresponds is provided with the opening, the opening with the bellying forms a holding chamber, ultrasonic transducer is whole or the part is arranged in the holding chamber, and with the structure direct or indirect contact is passed through to the sound.
In a further arrangement of the present invention, the housing of the ultrasonic transducer is connected to the mounting portion; alternatively, the housing of the ultrasonic transducer is integrally provided with the mounting portion.
Based on same utility model the design, the utility model also provides an elasticity test probe, including the aforesaid elasticity detection device, elasticity test probe still includes casing, drive assembly sets up in the casing, and be used for the drive the sound passes through the structure.
The utility model discloses a further setting, drive assembly includes:
a vibrator;
one end of the at least one transmission rod is connected with the vibrator, and the other end of the at least one transmission rod is connected with the ultrasonic transducer or the mounting part.
The utility model discloses a further setting still includes: a connecting device; the ultrasonic transducer is arranged on the connecting device, and the transmission rod is connected with the connecting device.
The utility model discloses a further setting, connecting device with be equipped with resilient gasket between the ultrasonic transducer.
In a further aspect of the present invention, the elastic detection probe further comprises a fixing portion, the fixing portion is disposed in the housing, and the ultrasonic transducer is disposed on the fixing portion; the transmission rod penetrates through the fixing part and is connected with the mounting part.
The utility model discloses a further setting, ultrasonic testing probe still includes: and the elastic medium is connected between the mounting part and the shell, or is connected between the connecting device and the shell.
Based on same utility model design, the utility model also provides an elasticity detecting system, it includes: the device comprises an ultrasonic signal receiving and transmitting unit, a low-frequency excitation unit, a data storage unit, a data analysis unit, a display unit, a main control unit and the elastic detection probe; wherein the content of the first and second substances,
the ultrasonic signal transceiving unit is respectively connected with the ultrasonic transducer and the main control unit and is used for exciting an array element in the ultrasonic transducer to generate ultrasonic waves and receiving ultrasonic echo signals;
the low-frequency excitation unit is respectively connected with the driving assembly and the main control unit and is used for driving the driving assembly to generate low-frequency vibration;
the main control unit is respectively connected with the data storage unit and the data analysis unit, and is used for controlling the data storage unit to collect and store ultrasonic echo signals, controlling the data analysis unit to read data of the data storage unit, and extracting B picture data reflecting tissue structure information and elastic information reflecting tissue hardness information, or ultrasonic signal attenuation information reflecting fatty liver degree;
the display unit is connected with the data analysis unit and used for displaying the information extracted by the data analysis unit.
To sum up, the utility model provides a structure, elasticity detection device, probe and system are passed through to sound, wherein, the structure is passed through to sound includes that the structure body is passed through to sound and sets up the bellying at structure body top is passed through to sound. The utility model discloses a sound that will be provided with the bellying passes through the structure setting at ultrasonic transducer's front end to through bellying low-frequency vibration treat the target in producing the shear wave waiting, not only realize image two-dimentional B image guide function, can also guarantee instantaneous elasticity detection quality.
Drawings
In order to clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to the structures shown in the drawings without creative efforts.
Fig. 1 is a schematic view of the overall structure of the middle elasticity detecting probe of the present invention.
Fig. 2 is a schematic structural diagram of the middle acoustic transmission structure of the present invention.
Fig. 3 is a schematic structural view of the integral movement of the middle acoustic transmission structure and the ultrasonic transducer of the present invention.
Fig. 4 is a schematic structural diagram 1 of the single movement of the middle acoustic transmission structure of the present invention.
Fig. 5 is a schematic structural diagram 2 of the single movement of the middle acoustic transmission structure of the present invention.
Fig. 6 is a schematic diagram of an array distribution of ultrasonic transducers.
Fig. 7 is a schematic structural view of the middle protruding portion of the present invention.
Fig. 8 is a schematic view of the position relationship between the convex portion and the rib according to the present invention.
Fig. 9 is a partial structural schematic diagram of the middle acoustic transmission structure of the present invention.
Fig. 10 is a functional block diagram of the elasticity inspection system according to the present invention.
Fig. 11 is a schematic diagram illustrating the echo signal depth information correction performed by the middle acoustic transmission structure of the present invention.
Fig. 12 is a schematic diagram of the vibration displacement signals present in the instant elastography of the present invention.
Fig. 13 is a schematic diagram of the extraction of shear wave velocity in the transient elastography of the present invention.
Fig. 14 is a schematic flow chart of the elasticity detection method according to the present invention.
In the drawings, the reference numbers: 100. an elastic detection probe; 101. a housing; 102. a drive assembly; 1021. a vibrator; 1022. A transmission rod; 103. an elasticity detecting device; 1031. an ultrasonic transducer; 10311. a first array; 10312. a second array; 1032. an acoustically transparent structure; 1033. a connecting member; 1034. an installation part; 1035. a sound-transmitting structural body; 1036. a boss portion; 1037. an elastic medium; 104. a connecting device; 105. a fixed part; 106. an elastic pad; 200. an ultrasonic signal transceiving unit; 300. a low-frequency excitation unit; 400. a data storage unit; 500. a data analysis unit; 600. a display unit; 700. and a main control unit.
Detailed Description
The utility model provides a structure, elasticity detection device, probe and system are passed through to sound, for making the utility model discloses a purpose, technical scheme and effect are clearer, make clear and definite, and it is right that the following reference is made to the attached drawing and the example is lifted the utility model discloses further detailed description. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.
In the embodiments and claims, the articles "a", "an", "the" and "the" may include plural forms as well, unless the context specifically dictates otherwise. If there is a description relating to "first", "second", etc. in the embodiments of the present invention, the description of "first", "second", etc. is for descriptive purposes only and is not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one of the feature.
It will be further understood that the terms "comprises" and/or "comprising," when used in this specification, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof. It will be understood that when an element is referred to as being "connected" or "coupled" to another element, it can be directly connected or coupled to the other element or intervening elements may also be present. Further, "connected" or "coupled" as used herein may include wirelessly connected or wirelessly coupled. As used herein, the term "and/or" includes all or any element and all combinations of one or more of the associated listed items.
It will be understood by those within the art that, unless otherwise defined, all terms (including technical and scientific terms) used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. It will be further understood that terms, such as those defined in commonly used dictionaries, should be interpreted as having a meaning that is consistent with their meaning in the context of the prior art and will not be interpreted in an idealized or overly formal sense unless expressly so defined herein.
In addition, the technical solutions in the embodiments may be combined with each other, but it must be based on the realization of those skilled in the art, and when the technical solutions are contradictory or cannot be realized, the combination of the technical solutions should not be considered to exist, and is not within the protection scope of the present invention.
Referring to fig. 1 to 9, the present invention provides a preferred embodiment of an elastic test probe.
As shown in fig. 1 to 4, the present invention provides an elasticity detecting probe 100, which includes a casing 101, a driving assembly 102 and an elasticity detecting device 103, wherein the elasticity detecting device 103 is disposed on the casing 101, and the driving assembly 102 is disposed in the casing 101. Wherein the elasticity detecting device 103 comprises: an ultrasonic transducer 1031 and a sound transmission structure 1032, wherein the sound transmission structure 1032 is arranged at the front end of the ultrasonic transducer 1031, and the driving component 102 is used for driving the sound transmission structure 1032 to vibrate. The acoustically transparent structure 1032 includes: a sound-transmitting structure body 1035, and a protrusion 1036 disposed at the top of the sound-transmitting structure body 1035.
Specifically, the ultrasonic transducer 1031 is a multi-array element ultrasonic transducer, and the array direction of the array elements of the ultrasonic transducer 1031 corresponds to the length direction of the surface of the protruding portion 1036, that is, the length direction of the protruding portion 1036 corresponds to the direction of the imaging surface of the ultrasonic transducer 1031. The ultrasonic transducer 1031 includes a first array 10311 and second arrays 10312 on both sides of the first array 10311, the protrusion 1036 is disposed right above the first array 10311, and a central axis of the protrusion 1036 coincides with a central axis of the first array 10311, as shown in fig. 6. During transient elastography, at least some of the elements of the first array 10311 are used to transmit and receive ultrasound signals to track and detect shear waves to improve the accuracy of transient elastography detection. The acoustically transparent structure 1032 is disposed at a front end of the ultrasonic transducer 1031 and is in direct or indirect contact with a subject to be detected. The acoustically transparent structure 1032 vibrates at a low frequency on the surface of the object to be detected by the convex portion 1036 and generates a shear wave under the driving of the driving assembly 102. During transient elastography detection, the driving component 102 drives the sound transmission structure 1032 to vibrate, so that two functions of two-dimensional imaging and high-quality transient elastography are considered.
The position of the protruding portion 1036 is not limited to the center position of the ultrasonic transducer 1031, and may be at other positions of the ultrasonic transducer array. In addition, the time for the detection of the start-up operation of the array element may be before the start of the vibration of the convex portion 1036, or may be after the start of the vibration of the convex portion 1036.
Referring to fig. 2 and 7, in a further configuration of an embodiment, a width d1 of a surface of the protrusion 1036 is 5-15mm.
Specifically, the surface of the protruding portion 1036 directly or indirectly acts on the surface of the detection target, and under the action of the mechanical vibration, the surface s of the protruding portion 1036 directly and oppositely vibrates with the skin. In order to be able to better generate a shear wave field suitable for transient elastography detection by vibration in the rib gap, the dimension d1 of the surface s of the protruding portion 1036 should not be too large, the width d1 of the protruding portion 1036 is 5-15mm, and the width direction corresponds to the rib gap direction, as shown in fig. 7. When a patient is examined, the raised portion 1036 is placed between the ribs, as shown in fig. 8. The array direction of the array elements of the ultrasonic transducer 1031 corresponds to the length direction d2 of the surface of the protruding portion 1036, and this arrangement facilitates two-dimensional imaging with a multi-array element ultrasonic transducer. The frequency range of the aforementioned low-frequency vibration is 0.01-10KHz, and preferably, the frequency range of the low-frequency vibration is 20-300Hz, for example, 200Hz.
Mechanical vibration is applied to the rib gap on the surface s of the protruding portion 1036, and the position of the rib is relatively fixed, so that under the action of the mechanical vibration, the skin tissue of the rib gap is pressed into the rib gap on the surface of the protruding portion 1036, and compared with the position where the rib is fixed, an obvious fault is formed, and the fault is favorable for generating shear waves. The dimension d1, which determines the size of the slice plane and directly has a large influence on the generated shear wave field, is located in the rib space. The dimension d1 should not be too large, and too large dimension can produce diffraction effect on the one hand, is unfavorable for elastic detection, and on the other hand is difficult to place in rib clearance, also is unfavorable for elastic detection. Dimension d1 is consistent with the range of conventional instantaneous elastography probe sizes, typically 5mm,7mm,10mm for the three model S, M, XL probes, respectively. The model S is suitable for children with narrow rib gaps, and the probe of the model M is adopted for normal adults, and the probe of the model XL with larger size is adopted for obese patients.
Referring to fig. 2 and fig. 7, further, the length of the end surface of the protruding portion 1036 is less than twice the width of the end surface of the protruding portion 1036.
Specifically, the length of the end face of the protruding portion 1036, that is, the dimension parallel to the rib direction is d2, and the dimension d2 also has an influence on the generation of the shear wave field, but the influence on the generation of the shear wave field is smaller than that on the dimension d1, because the protruding portion 1036 lacks the rib supporting function when vibrating in the direction parallel to the rib, the formed fault strength is weaker, and therefore the influence on the shear wave field is smaller. The appropriate increase of the size d2 facilitates two-dimensional imaging of the multi-element ultrasonic transducer 10313 placed behind it, but at the same time takes into account the diffraction effect caused by the oversize, wherein the relationship between the size d1 and the size d2 is: d2<2 × d1.
Referring to fig. 2 and 3, in a further configuration of an embodiment, the protrusion 1036 is cylindrical or truncated cone-shaped.
Specifically, the shape of the protruding portion 1036 is approximately cylindrical, elliptic cylindrical, or truncated cone, but is not limited to the above shape, for example, the shape may also be a rectangular parallelepiped, and then the shape of the surface of the protruding portion 1036 may be circular, elliptic, square, or the like, and meanwhile, the surface of the protruding portion 1036 may also be a convex surface or a concave surface. In order to improve the comfort of the user, the protruding portion 1036 is generally shaped like a cylinder or a truncated cone. For example, when the protruding portion 1036 is an elliptical column, the cross section of the protruding portion 1036 has an elliptical shape, and the end surface thereof is also an ellipse. Wherein, in order to ensure the instant elastography detection quality, the vertical height between the surface of the protruding portion 1036 and the upper surface of the ultrasonic transducer 1031 is 2-30mm, for example, may be 15mm.
Referring to fig. 2 and 9, in a further configuration of an embodiment, two extension sections of the surface width direction of the protruding portion 1036 respectively form an angle of 0 to 30 degrees with a central axis of the protruding portion 1036.
Specifically, the extension section is located on the opposite side of the protruding portion 1036, and the extension section and the protruding portion 1036 are distributed in a central symmetry manner. An included angle between the extension tangent plane and the central axis of the protruding portion 1036 is 0-30 degrees and is similar to a plane, so that in the vibrating process, the portion, located between the two extension tangent planes, of the protruding portion 1036 can enter gaps between ribs without blocking, and effective vibration is formed. In one implementation, the angle between the out-extending tangent plane and the central axis of the protrusion 1036 may be 0 °.
Referring to fig. 2-4, in a further arrangement of an embodiment, the acoustically transparent structure 1032 is disposed coaxially with the ultrasonic transducer 1031; the protruding portion 1036 is coaxially disposed with the acoustically transparent structure body 1035.
Specifically, the protruding portion 1036 is integrally disposed with the acoustically transparent structure body 1035, and the acoustically transparent structure 1032 is disposed coaxially with the ultrasonic transducer 1031, that is, the protruding portion 1036 is also disposed coaxially with the ultrasonic transducer 1031, so that an ultrasonic signal emitted by the ultrasonic transducer 1031 can be transmitted out of the acoustically transparent structure 1032, and detection of an ultrasonic signal of a detection target is achieved through the acoustically transparent structure 1032.
In some embodiments, in order to make the convex part comfortable to contact with the skin of the human body, the corners of the end face of the convex part are in a shape of a rounded corner or an inverted triangle.
Referring to fig. 3 to fig. 5, in a further configuration of an embodiment, the elasticity detecting device 103 further includes: a mounting section 1034; the mounting section 1034 is disposed at the bottom of the acoustically transparent structure 1032.
Specifically, the mounting portion 1034 is provided with an opening corresponding to the ultrasonic transducer 1031, the opening and the protruding portion 1036 form a second cavity (not labeled in the figure), and the ultrasonic transducer 1031 is placed in the second cavity and is in direct or indirect contact with the sound transmission structure 1032.
The acoustically transparent structure 1032 is disposed on the mounting portion 1034. The ultrasonic transducer 1031 may be received in a second cavity formed by the mounting portion 1034 and the raised portion 1036 and may be in direct or indirect contact with the acoustically transparent structure 1032. Thus, the mounting portion 1034 is not limited to be made of a sound-transmitting material, as long as the ultrasonic transducer 1031 and the protruding portion 1036 can form an ultrasonic wave propagation channel therebetween. In some embodiments, the acoustically transparent structure 1032 and the mounting portion 1034 may be integrally formed.
Referring to fig. 3-5, in a further implementation of an embodiment, the acoustically transparent structure 1032 is movable alone or integrally with the ultrasound transducer 1031.
Referring to fig. 3-5, in some embodiments, the driving assembly 102 includes: the ultrasonic transducer device comprises a vibrator 1021 and at least one transmission rod 1022, wherein one end of the transmission rod 1022 is connected with the vibrator 1021, and the other end of the transmission rod 1022 is connected with the ultrasonic transducer 1031 or the mounting portion 1034.
Specifically, when the acoustically transparent structure 1032 and the ultrasonic transducer 1031 are integrally moved, the transmission rod 1022 is connected to the mounting portion 1034 or the ultrasonic transducer 1031 to synchronously drive the ultrasonic transducer 1031 and the acoustically transparent structure 1032 to vibrate, as shown in fig. 5. When the acoustically transparent structure 1032 vibrates alone, the driving link 1022 is coupled to the mounting portion 1034 to drive the acoustically transparent structure 1032 alone to vibrate, as shown in fig. 4. In some embodiments, there may be 2 or 4 drive rods 1022.
When the acoustically transparent structure 1032 is integrally movable with the ultrasonic transducer 1031, the ultrasonic transducer 1031 is directly or indirectly connected to the acoustically transparent structure 1032.
For example, when the ultrasonic transducer 1031 is directly connected to the acoustically transparent structure 1032, in one implementation, the housing of the ultrasonic transducer 1031 is adhered to the mounting portion 1034, or the housing of the ultrasonic transducer 1031 is integrally disposed with the mounting portion 1034. The ultrasound transducer 1031 is directly connected to the acoustically transparent structure 1032 as shown in fig. 5.
Specifically, the acoustically transparent structure 1032 and the ultrasonic transducer 1031 may be connected and fixed by an adhesive manner, so as to ensure that the upper surface of the ultrasonic transducer 1031 is tightly attached to the mounting portion 1034 or the protruding portion 1036. In addition, the mounting portion 1034 may also serve as a housing of the ultrasonic transducer 1031, so that the acoustically transparent structure 1032 is integrally disposed with the ultrasonic transducer 1031, thereby achieving the close fit between the ultrasonic transducer 1031 and the mounting portion 1034 or the protruding portion 1036.
Referring to fig. 3, in a further implementation of an embodiment, when the ultrasound transducer 1031 is indirectly connected to the acoustically transparent structure 1032, the ultrasound detection probe further includes: a connecting device 104, wherein the ultrasonic transducer 1031 is disposed on the connecting device 104, the ultrasonic transducer 1031 is indirectly connected to the acoustically transparent structure 1032 through the connecting device 104, and the transmission rod 1022 is connected to the connecting device 104.
Specifically, a groove structure (not shown) is disposed on the connecting device 104, and the ultrasonic transducer 1031 is clamped with the connecting device 104 through the groove structure. The transmission rod 1022 is connected to the connecting device 104, and the driving assembly 102 drives the connecting device 104 to synchronously drive the ultrasonic transducer 1031 and the acoustically transparent structure 1032 to vibrate.
With continuing reference to fig. 3, further, an elastic pad 106 is disposed between the connecting device 104 and the ultrasonic transducer 1031, the elastic pad 106 is disposed at the bottom of the recess structure, and after the ultrasonic transducer 1031 is mounted on the connecting device 104, an upward force is applied to the ultrasonic transducer 1031, so that the connection between the ultrasonic transducer 1031 and the acoustically transparent structure 1032 is tighter. In one implementation, the resilient gasket 106 may be a rubber gasket.
In another implementation, a transition structure (not shown) is disposed between the acoustically transparent structure 1032 and the ultrasound transducer 1031, the transition structure is made of an acoustically transparent material, an ultrasound signal can pass through the transition structure, and the ultrasound transducer 1031 and the acoustically transparent structure 1032 are connected through the transition structure. The transition structure may be a capsule having an elastic membrane, or may be made of an acoustically transparent elastic pad having a certain elasticity, and a compressed force may be provided by the elasticity of the transition structure, and the force may ensure that the transition structure and the acoustically transparent structure 1032 and the transition structure and the detection surface of the ultrasonic transducer 1031 are attached more tightly, so as to ensure that no gap exists between the acoustically transparent structure 1032 and the ultrasonic transducer 1031, which is favorable for the transmission of an ultrasonic signal.
Wherein, the utility model discloses a drive assembly 102 drives ultrasonic transducer 1031 with the synchronous vibration of sound transmission structure 1032 can avoid sound transmission structure 1032 with mechanical shock phenomenon between the ultrasonic transducer 1031 has avoided in the vibration process sound transmission structure 1032 with produce the clearance between the ultrasonic transducer 1031, makes at the vibration in-process sound transmission structure 1032 with ultrasonic transducer 1031 keeps the state of closely laminating, has guaranteed to arrange in sound transmission structure 1032 rear ultrasonic signal that ultrasonic transducer 1031 sent can be unbroken propagate smoothly to being detected in organizing, has both avoided sound transmission structure 1032 with ultrasonic transducer 1031 produces mechanical vibration and causes the influence to the detection and the formation of image of ultrasonic signal. Meanwhile, damage to the surface of the ultrasonic transducer 1031 caused by mechanical impact between the acoustically transparent structure 1032 and the ultrasonic transducer 1031 during vibration is also avoided.
Referring to fig. 4, when the acoustically transparent structure 1032 is separately activated, a connection 1033 is provided between the ultrasonic transducer 1031 and the acoustically transparent structure 1032.
Specifically, when the driving assembly 102 drives the sound transmission structure 1032 to vibrate independently, a gap is generated between the ultrasonic transducer 1031 and the sound transmission structure 1032, and by providing a connecting member 1033 between the ultrasonic transducer 1031 and the sound transmission structure 1032, the connecting member 1033 has sound transmission and deformation capabilities, and when the sound transmission structure 1032 vibrates, the connecting member can move along with the sound transmission structure 1032. The connector 1033 maintains the connection between the acoustically transparent structure 1032 and the ultrasonic transducer 1031 to avoid a problem that the ultrasonic signal cannot propagate due to a gap generated when the acoustically transparent structure 1032 vibrates alone.
It should be noted that the action of the acoustically transparent structure 1032 alone includes a case where the ultrasonic transducer 1031 is able to vibrate in the opposite direction of the acoustically transparent structure 1032 when the acoustically transparent structure 1032 vibrates alone.
In one implementation, the connector 1033 can be an elastic acoustically transparent bladder connected between the ultrasonic transducer 1031 and the acoustically transparent structure 1032. Wherein, the elastic sound transmission capsule body is internally provided with a sound transmission medium. The sound transmission medium can be a medium in which ultrasonic signals such as water and glycerol can propagate.
Specifically, the elastic acoustic transmission capsule is attached to the surface of the ultrasound transducer 1031 and the surface of the acoustic transmission structure 1032, and a sound transmission medium capable of transmitting an ultrasound signal is disposed in the elastic acoustic transmission capsule, and when the acoustic transmission structure 1032 vibrates alone, the elastic acoustic transmission capsule can generate a certain deformation under the pulling of the acoustic transmission structure 1032, and the deformation can keep the connection between the acoustic transmission structure 1032 and the ultrasound transducer 1031, so that the ultrasound signal emitted by the ultrasound transducer 1031 can be smoothly transmitted to a detection target through the acoustic transmission structure 1032 without being blocked.
Referring to fig. 4, in some embodiments, when the acoustically transparent structure 1032 is vibrated alone, the ultrasound inspection probe further includes: a fixing part 105, the fixing part 105 being disposed inside the housing 101, the ultrasonic transducer 1031 being disposed on the fixing part 105; the transmission rod 1022 passes through the fixing portion 105 and is connected to the mounting portion 1034.
Specifically, the fixing portion 105 is fixedly connected to the housing 101, and the ultrasonic transducer 1031 is disposed on the fixing portion 105 or directly fixedly connected to the housing 101. A through hole (not shown) is formed in the fixing portion 105, through which the transmission rod 1022 passes, when the driving assembly 102 drives the acoustically transparent structure 1032 to vibrate, the transmission rod 1022 vibrates in the through hole, the fixing portion 105 does not vibrate with the ultrasonic transducer 1031, the acoustically transparent structure 1032 is connected with the transmission rod 1022, or the transmission rod 1022 is connected with the mounting portion 1034, so as to drive the acoustically transparent structure 1032 to vibrate independently, wherein an ultrasonic signal propagation path between the acoustically transparent structure 1032 and the ultrasonic transducer 1031 can be realized through the connecting member 1033.
Referring to fig. 1, in a further implementation of an embodiment, the ultrasound inspection probe further includes: and an elastic medium 1037, wherein the elastic medium 1037 is connected between the mounting portion 1034 and the housing 101.
Specifically, the mounting section 1034 is connected to the housing 101, either directly or indirectly, via an elastic medium 1037 to form a closed ultrasonic test probe. The elastic medium 1037 has a stretching function, so that the sound transmission structure 1032 can be driven by the vibrator 1021 to vibrate and is kept connected with the housing 101.
It should be noted that, if the ultrasonic transducer 1031 is mounted on the connecting device 104, the elastic medium 1037 may be disposed between the connecting device 104 and the housing 101.
Referring to fig. 10, in some embodiments, the present invention further provides an elasticity detecting system, which includes: the ultrasonic signal transceiver unit 200, the low frequency excitation unit 300, the data storage unit 400, the data analysis unit 500, the display unit 600, the main control unit 700, and the elasticity test probe 100 as described above. The ultrasonic signal transceiving unit 200 is connected to the ultrasonic transducer 1031 and the main control unit 700, respectively, and is configured to excite an array element in the ultrasonic transducer 1031 to generate an ultrasonic wave and receive an ultrasonic echo signal; the low-frequency excitation unit 300 is respectively connected to the driving assembly 102 and the main control unit 700, and is configured to drive the driving assembly 102 to generate low-frequency vibration; the main control unit 700 is respectively connected to the data storage unit 400 and the data analysis unit 500, and is configured to control the data storage unit 400 to collect and store the ultrasound echo signals, and control the data analysis unit 500 to read data in the data storage unit 400, and extract B-diagram data reflecting tissue structure information and elasticity information reflecting tissue hardness information, or ultrasound signal attenuation information reflecting fatty liver degree; the display unit 600 is connected to the data analysis unit 500, and is configured to display the information extracted by the data analysis unit 500, that is, to display an output result of the data analysis unit 500.
It should be noted that, the ultrasonic signal transceiving unit 200, the low frequency excitation unit 300, the main control unit 700, the data storage unit 400, the data analysis unit 500 and the display unit 600 may be partially or entirely integrated into the elastic detection probe 100, or may be disposed in a host outside the elastic detection probe 100. The connection of the signals or the transmission of the data may be a wired transmission or a wireless transmission.
When the detection system based on the elasticity detection probe detects a patient, two imaging modes are provided, namely a conventional B-image imaging mode and a transient elasticity imaging detection mode. During detection, the bulge part of the sound transmission structure at the front end of the elastic detection probe is placed in a gap between the bulge part and two ribs close to the liver, the initial position of the elastic detection probe is approximately vertical to the surface of the skin, and couplers are added at the contact position and the peripheral position of the sound transmission structure and the ribs, so that the bulge part is fully contacted with the skin on the surfaces of the ribs, and B-picture imaging and elastic detection are facilitated. Even though the B-map imaging range is still limited to some extent by the size of the end face length dimension of the projections, there has been a significant improvement in image guidance over the Shan Zhenyuan ultrasonic transducer. When detecting a patient, firstly, a B image imaging mode is started: under the control of the main control unit, the ultrasonic signal transceiving unit drives the second array and the first array elements of the ultrasonic transducer to excite ultrasonic signals and receive echo signals of ultrasonic waves, the data storage unit collects and stores the echo signals, the data analysis unit processes and analyzes the stored echo data, a two-dimensional image which can reflect an anatomical structure of tissues can be obtained, the two-dimensional image is usually an ultrasonic B picture, whether an imaging area contains large blood vessels, biliary tracts or local focuses can be observed through the B picture, the imaging areas can be avoided through observation, and then the image guide function is realized. The two-dimensional imaging data is then fed to a display unit and displayed on a display. The operator can effectively select the imaging position and the area suitable for instantaneous elasticity detection according to the B picture image presented on the display, and avoid the area containing large blood vessels or local focuses and other uneven images influencing the instantaneous elasticity detection result.
After a proper position is selected, a certain pressure is applied to the composite probe along the detection direction, the pressing force of the gap between the convex part of the sound transmission structure and the rib is increased, and after an operator sees that the pressure value reaches an expected value, instantaneous elastography detection can be carried out by pressing a starting switch arranged on the shell of the elastic detection probe. At the moment, the low-frequency excitation unit outputs a low-frequency signal after passing through the power amplifier, the low-frequency signal drives a driving assembly in the elastic detection probe, the driving assembly drives the sound transmission structure to generate instantaneous vibration together, the protruding portion vibrates among ribs, and shear waves are generated inside a human body.
When the switch is started, the ultrasonic signal transceiving unit adds or switches a shear wave detection tracking mode, and drives at least part of array elements of the first array of the ultrasonic transducer to complete the transmission and the reception of the ultrasonic. In the transient elastography detection, a shear wave field generated right below a convex part of the vibration component is mainly analyzed, so that only at least part of array elements of the first array corresponding to the convex part of the vibration component are needed to excite ultrasonic signals. This partial array element position is the symmetric distribution with the center of the bellying on sound transmission structure top, and the scope size that distributes is not more than the horizontal size of the bellying of sound transmission structure, can be that single array element is used for shear wave to track, also can be that a plurality of array elements that are the central axis symmetry are used for shear wave to track. The partial array elements track and detect the propagation process of the shear wave right below the sound transmission structure along the depth direction in a pulse-echo and high frame rate acquisition mode. The data storage unit collects and stores echo signals containing shear wave propagation information, the data processing and analyzing unit reads and analyzes the data, and finally gives results such as elasticity detection information capable of reflecting the softness and hardness of tissues and fat grade information capable of reflecting the fat content of liver tissues, and the like, wherein the information can be specific numerical values or grade classification of lesion severity. And finally, displaying the elastic detection result by the display unit, and finishing the elastic detection.
Specifically, the ultrasonic echo RF signal is directly subjected to A/D acquisition and storage through primary amplification. The depth position information correction is carried out on the echo signal of each array element, and the correction process is mainly used for solving or optimizing the influence on the ultrasonic echo signal caused by the addition of the acoustic transmission structure. In the conventional treatment, since the detected tissue is usually a relatively complex tissue structure, the propagation speed of the default ultrasonic signal in the detected tissue is a fixed value (1540 m/s) for the convenience of treatment, while the acoustic transmission structure adopted in the present invention is a structure whose shape can be determined or fixed, and the accurate propagation speed of the ultrasonic wave in the structure can be obtained in advance. When the propagation speed deviates from 1540m/s, the necessity of depth position information correction of the array echo signal exists, especially when the deviation speed is relatively high, if the correction is not carried out, the image depth position information deviates.
For a better understanding, the following is exemplified here. As shown in fig. 11, a linear array probe is used to image 6 pentagons at different lateral positions and the same depth within an imaging range, and if there is no acoustic transmission structure device, the propagation distances and propagation speeds of echo emission signals of array elements corresponding to the 6 pentagons are the same in the imaging result, so that the imaging still shows the same depth. If the acoustic transmission structure is arranged on the surface of the linear array probe, when the propagation speed of the ultrasonic signal in the acoustic transmission structure is high (more than 1540 m/s), the ultrasonic signal propagates at the same distance (the object with the same depth is detected), when the ultrasonic signal passes through the acoustic transmission structure in the propagation path, the propagation time is shortened, and the ultrasonic signal is reflected in shallow position in imaging. The more the distance of the acoustic transmission structure is passed through, the shallower the position is, and the imaging positions (hollow pentagram) of 6 pentagrams are different along with the difference of the distance of the acoustic transmission structure envelope from the array element.
If the distance from the surface of the acoustic transmission structure to the surface of the array element is known as the envelope s (n), and n is the array element sequence, the time required for detecting the distance depth by the ultrasonic signal is t1=2*s (n)/C, wherein C is the propagation speed of the ultrasonic in the acoustic transmission structure. When there is no insonification structure, the time required for the ultrasonic signal to detect the equidistance s (n) is t2=2*s (n)/1540 m/s, then there is a time difference t1-t2, and then the corresponding depth correction magnitude Δ d =1540 (t 1-t 2). After the delta d is obtained, the real position can be corrected, and the corrected signal is subjected to subsequent processing.
The ultrasonic echo signals are divided into ultrasonic echo signals for two-dimensional imaging and ultrasonic signals for elastic shear wave velocity extraction according to different imaging modes. The utility model mainly has two imaging modes, one is a B image imaging mode for realizing two-dimensional image guide function, and all array elements of the ultrasonic transducer participate in the transmission and the reception of ultrasonic signals in the mode; one mode is an elastic detection imaging mode for tracking shear waves generated by mechanical vibration, in the mode, only array elements of a part of multi-array-element ultrasonic transducers are excited to generate ultrasonic signals, and the tracking and the detection of the shear waves are realized in a pulse-echo and high-frame-rate mode. In the B-image imaging mode, the processing of the ultrasonic echo signal mainly includes a series of processes such as signal primary filtering, time gain compensation, quadrature demodulation, envelope extraction, beam forming, and image optimization post-processing, and finally a two-dimensional grayscale image that can reflect the tissue ablation structure, which is generally called a B-map, can be obtained. Whether the imaging area contains large blood vessels, biliary tracts or local focuses can be observed through the B picture, and the imaging areas can be avoided through observation, so that the image guiding function is realized.
In the elastic detection imaging mode, the main purpose of processing the ultrasonic echo signals is to extract the vibration information of tissue particles caused in the shear wave propagation process, further analyze the propagation speed of the shear wave and finally realize elastic imaging. The method for extracting the vibration displacement by using the ultrasonic pulse echo signal mainly comprises the following steps: cross-correlation algorithms, phase-shift-based algorithms and cross-spectra. The utility model discloses in adopt phase place skew algorithm, main processing procedure as follows: two signals can be obtained by performing quadrature demodulation on the ultrasonic echo RF signal: an in-phase component I and a quadrature component Q. The displacement of the two frames of RF signals relative to each other can be calculated by the amount of phase shift corresponding to the heart rate in the two adjacent frames. Assuming that the RF signals of two adjacent frames are denoted as a (t) and b (t), the cross-correlation function of the two signals can be defined as
The magnitude of the time delay of the two signals can be determined by means of a cross-correlation function according to equation (2)
In equation (2), the imaginary and real parts of the cross-correlation function are represented by Im and Re, respectively, and the center frequency of the RF signal is represented by ω 0 And (4) showing. Substituting formula (1) into formula (2) can obtain a relative displacement of
In the formula (3), c represents the propagation velocity of the ultrasound, and the center frequency of the ultrasound is represented by f c It is shown that the window length is M and the sequence numbers of adjacent RF signals are denoted by n and n + 1. In this one-dimensional algorithm, the center frequency f is assumed c And (4) determining. In reality, the center frequency is not an absolute constant value, and the calculation formula of the two-dimensional cross-correlation algorithm is expressed as follows in consideration of the change of the center frequency:
the method has high calculation precision. The vibration displacement signal obtained by the above calculation is shown in fig. 12.
By using the processing method, the time-varying process of the particle displacement generated by the tissue particles at different depths along the axial depth direction at the mechanical vibration position in the process of shear wave propagation can be obtained. The vibration displacement throughout the process from the excitation of the shear wave to the end of the detection of the vibration is shown in fig. 11. The whole displacement variation process comprises excitation of the shear wave, downward propagation of the shear wave and reflection of the shear wave. Starting from 20ms, the acoustically transparent structure is driven by the vibrating device to vibrate instantaneously, so that the relative displacement between the top end of the acoustically transparent structure and the detected object changes, and the frequency of the change in the displacement corresponds to the shear wave excitation frequency to some extent, as shown in a region a in fig. 12. Not only shear waves but also longitudinal waves are generated during this time. Because the propagation speed of the longitudinal wave is very high (up to 1000 m/s), the detection and the recording of the longitudinal wave cannot be realized by utilizing the ultrasonic echo technology, and the propagation speed of the shear wave (1-10 m/s) is lower, so that the longitudinal wave can be detected by utilizing the ultrasonic wave. A process in which a single shear wave component propagates from the top down in the depth direction may be observed for a subsequent period of time, as shown by B in fig. 12. The slope of the propagation track of the shear wave in the region reflects the speed of the shear wave propagating in the depth direction, and the higher the slope is, the higher the propagation speed of the shear wave is. In fig. 12C is the reflection process of the shear wave. In the process of analyzing transient elastography data, we generally analyze only a single shear wave component in the B portion of the region, and extract the relevant data of the B portion, and similar results can be obtained as shown in fig. 13 (a).
There are various methods for obtaining the shear wave velocity, and the analysis procedure for obtaining the shear wave velocity by the radon transform method is as follows. The dashed line in fig. 13 (a) reflects the propagation trajectory of the shear wave, and the radon transform is performed on the propagation trajectory to obtain fig. 13 (b), in which the angle of the maximum point (Peak histogram Value) corresponds to the angle between the shear wave trajectory and the horizontal direction, and the relational expression is
tan(θ)＝N x /N t , (5)
Wherein N is x And N t The numbers of pixel points in the depth direction and the time direction in fig. 13 (a) are shown, respectively, and it can be seen that
N x ＝x t /Δx, N t ＝t t /Δt (6)
Wherein x t For shear waves at propagation time t t The actual distance of the internal propagation along the depth direction, and Δ x and Δ t respectively represent the actual distance and time between pixel points along the depth direction and the time direction, and the actual distance and time can be known from the shear wave velocity C s In a relationship of
C s ＝x t /t t . (7)
By substituting expressions (5) and (6) into expression (7), the shear wave velocity C can be obtained s Is composed of
The shear wave velocity can also be obtained by using the relation between the shear wave propagation time and the propagation distance, linear fitting is carried out through the time-displacement relation of the peak point, and the obtained fitting slope corresponds to the shear wave velocity. At the obtained shear wave velocity c t Then, the equation μ = ρ c can be followed t 2 The shear modulus μ is obtained, where ρ is the soft tissue density (typically ρ =1 kg/m) 3 ) And then elastic imaging is realized.
In the elastography mode, the processing of the ultrasonic echo signals can extract not only the elasticity information of the tissues, but also the fat content information in the liver. The propagation attenuation of the ultrasonic wave in the medium is related to the amplitude and the property of the medium, when the amplitude is fixed, the attenuation is more serious when the viscosity of the medium is larger, and the fat change value of the liver is quantified by calculating the attenuation degree of the amplitude of the ultrasonic wave in the liver. The corresponding fat content assessment information may also be obtained by calculating the rate of change of the attenuation of the center frequency of the ultrasound echo signal RF with depth.
Referring to fig. 14, in some embodiments, the present invention further provides an elasticity detecting method applied to the elasticity detecting system, including the steps of:
s100, sending ultrasonic waves to a target area, and receiving echo signals of the ultrasonic waves; acquiring a difference value between the propagation speed of the ultrasonic wave in the sound transmission structure and the propagation speed in a preset tissue, and if the propagation speed of the ultrasonic wave is deviated from the propagation speed in the preset tissue, performing depth information correction on the echo signal;
s200, obtaining a two-dimensional image of a target area according to the echo signal corrected by the depth information;
s300, determining a detection position according to the two-dimensional image;
s400, applying mechanical vibration to the detection position to generate shear waves;
s500, transmitting ultrasonic waves for tracking the shear waves to the detection position, and receiving the ultrasonic waves of the target area to obtain ultrasonic echo data; the ultrasonic echo data is elastic information reflecting tissue hardness information or ultrasonic signal attenuation information reflecting fatty liver degree;
s600, obtaining and displaying a detection result of the detection position according to the ultrasonic echo data. As described in detail for an elasticity detection system, it is not described herein again.
It is to be understood that the invention is not limited to the above-described embodiments, and that modifications and variations may be made by those skilled in the art in light of the above teachings, and all such modifications and variations are intended to be included within the scope of the invention as defined in the appended claims.
Claims (29)
1. An elasticity detecting apparatus, comprising:
an ultrasonic transducer; the ultrasonic transducer is a multi-array element ultrasonic transducer;
a sound transmission structure disposed at a front end of the ultrasonic transducer;
the acoustically transparent structure includes:
a sound-transmitting structural body;
the bulge is arranged at the top of the sound transmission structure body.
2. The elasticity detection device of claim 1, wherein the boss is disposed coaxially with the acoustically transparent structural body.
3. The elasticity inspection device of claim 1, wherein the boss vibration generates shear waves in the inspection target.
4. The resiliency detection device of claim 1, wherein the boss is provided integrally with the acoustically transparent structural body.
5. The elasticity inspection device of claim 1, wherein the angle between each of two tangential planes extending in the width direction of the surface of the protrusion and the central axis of the protrusion is 0 to 30 degrees.
6. The elasticity inspection device according to claim 1, wherein the width of the surface of the protrusion is 5 to 15mm.
7. The apparatus according to claim 1, wherein the protrusion is cylindrical or truncated cone-shaped.
8. The elasticity detection device according to any one of claims 1 to 7, wherein a length of the end surface of the convex portion is less than twice a width of the end surface of the convex portion.
9. The elasticity detection device of claim 1, wherein the ultrasonic transducer comprises a first array and a second array located on both sides of the first array, the protrusion is disposed directly above the first array, and a central axis of the protrusion coincides with a central axis of the first array.
10. The elastography device of claim 9, wherein at least some of the array elements of the first array are configured to transmit and receive ultrasound signals to track and detect shear waves during transient elastography.
11. The apparatus according to claim 1, wherein the array direction of the array elements of the ultrasonic transducer is arranged corresponding to the length direction of the surface of the protrusion.
12. The elasticity detection device of claim 1, wherein the acoustically transparent structure is movable alone or in combination with the ultrasound transducer.
13. The apparatus according to claim 12, wherein the ultrasound transducer is directly or indirectly connected to the acoustically transparent structure when the acoustically transparent structure is integrally movable with the ultrasound transducer.
14. The elasticity detection device of claim 13, wherein a transition structure is disposed between the acoustically transparent structure and the ultrasonic transducer.
15. The elasticity detection device of claim 12, wherein a connector is disposed between the ultrasound transducer and the acoustically transparent structure when the acoustically transparent structure is independently movable.
16. The elasticity detection device of claim 15, wherein the connector is an elastic sound-permeable bag connected between the ultrasound transducer and the sound-permeable structure; wherein, the elastic sound transmission bag is internally provided with a sound transmission medium.
17. The elasticity detection device of claim 16, wherein the acoustically transparent medium is acoustically transparent.
18. The elasticity detection device of claim 1, wherein the acoustically transparent structure is disposed coaxially with the ultrasonic transducer.
19. The elasticity detection device according to claim 1, further comprising: an installation part; the installation part is arranged at the bottom of the sound transmission structure.
20. The resiliency detection apparatus of claim 19 wherein the acoustically transparent structure is integrally formed with the mounting portion.
21. The elasticity detection device of claim 20, wherein an opening is disposed at a position of the mounting portion corresponding to the ultrasonic transducer, the opening and the protrusion form a receiving cavity, and the ultrasonic transducer is disposed in the receiving cavity in whole or in part and is in direct or indirect contact with the sound transmission structure.
22. The device of claim 19 or 20, wherein the housing of the ultrasonic transducer is connected to the mounting portion; alternatively, the housing of the ultrasonic transducer is integrally provided with the mounting portion.
23. An elastography probe comprising the elastography device of claim 19, further comprising a housing, a drive assembly disposed within the housing and configured to drive the acoustically transparent structure.
24. The spring inspection probe of claim 23 wherein the drive assembly includes:
a vibrator;
one end of the at least one transmission rod is connected with the vibrator, and the other end of the at least one transmission rod is connected with the ultrasonic transducer or the mounting part.
25. The elastic inspection probe of claim 24, further comprising: a connecting device; the ultrasonic transducer is arranged on the connecting device, and the transmission rod is connected with the connecting device.
26. The elastomeric inspection probe of claim 25 wherein an elastomeric shim is provided between the attachment means and the ultrasonic transducer.
27. The elastic inspection probe of claim 24, further comprising: a fixed part; the fixing part is arranged in the shell, and the ultrasonic transducer is arranged on the fixing part; the transmission rod penetrates through the fixing part and is connected with the mounting part.
28. The spring inspection probe of claim 25 further comprising: and the elastic medium is connected between the mounting part and the shell, or the elastic medium is connected between the connecting device and the shell.
29. An elasticity detection system, comprising: an ultrasonic signal transceiving unit, a low frequency excitation unit, a data storage unit, a data analysis unit, a display unit, a main control unit and the elasticity detection probe of any one of claims 23 to 28; wherein, the first and the second end of the pipe are connected with each other,
the ultrasonic signal transceiving unit is respectively connected with the ultrasonic transducer and the main control unit and is used for exciting an array element in the ultrasonic transducer to generate ultrasonic waves and receiving ultrasonic echo signals;
the low-frequency excitation unit is respectively connected with the driving assembly and the main control unit and is used for driving the driving assembly to generate low-frequency vibration;
the main control unit is respectively connected with the data storage unit and the data analysis unit, and is used for controlling the data storage unit to collect and store ultrasonic echo signals, controlling the data analysis unit to read data of the data storage unit, and extracting B picture data reflecting tissue structure information and elastic information reflecting tissue hardness information, or ultrasonic signal attenuation information reflecting fatty liver degree;
the display unit is connected with the data analysis unit and used for displaying the information extracted by the data analysis unit.
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