CN101600392A - Use adjustable fluid lenses motion to be carried out the method and apparatus of ultrasound detection - Google Patents
Use adjustable fluid lenses motion to be carried out the method and apparatus of ultrasound detection Download PDFInfo
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- CN101600392A CN101600392A CNA2008800029144A CN200880002914A CN101600392A CN 101600392 A CN101600392 A CN 101600392A CN A2008800029144 A CNA2008800029144 A CN A2008800029144A CN 200880002914 A CN200880002914 A CN 200880002914A CN 101600392 A CN101600392 A CN 101600392A
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- G—PHYSICS
- G10—MUSICAL INSTRUMENTS; ACOUSTICS
- G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
- G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
- G10K11/18—Methods or devices for transmitting, conducting or directing sound
- G10K11/26—Sound-focusing or directing, e.g. scanning
- G10K11/30—Sound-focusing or directing, e.g. scanning using refraction, e.g. acoustic lenses
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/42—Details of probe positioning or probe attachment to the patient
- A61B8/4272—Details of probe positioning or probe attachment to the patient involving the acoustic interface between the transducer and the tissue
- A61B8/4281—Details of probe positioning or probe attachment to the patient involving the acoustic interface between the transducer and the tissue characterised by sound-transmitting media or devices for coupling the transducer to the tissue
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/48—Diagnostic techniques
- A61B8/488—Diagnostic techniques involving Doppler signals
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Abstract
A kind of system (200) that is used to detect the intravital motion of body comprises sonic probe (242,100), MEC (270), variable voltage source (290) and controller (210).Sonic probe (242,100) comprises sonic transducer (244,20) and is coupled to the variable refraction acoustic lens (242,10) of this sonic transducer.Variable refraction acoustic lens have at least pair of electrodes (150,160a, 160b), described variable refraction acoustic lens is suitable for regulating in response to the selection voltage that applies at the electrode two ends at least one characteristic of variable refraction acoustic lens.MEC is coupled to sonic transducer, and execution algorithm is to come the motion of detected object in response to the acoustic energy that is received by sonic transducer.Variable voltage source applies selection voltage to described counter electrode.Controller control variable voltage source is to apply described selection voltage to described counter electrode.
Description
The present invention relates to acoustic imaging method, acoustic imaging device, and relate more specifically to use acoustical signal and adjustable fluid lenses to detect the method and apparatus of the intravital motion of body.
Detecting the intravital motion of body is the technical goal that a lot of medical imagings are used.A lot of image modes such as computer tomography (CT), PET (positron emission tomography) (PET) or nuclear magnetic resonance (MRI) are gathered imaging plane or volume with the sufficiently long time, so that are caused the picture quality of the standard that do not reach by patient respiratory circulation, heart movement or the kinetic athletic meeting of patient's muscular tissue.In addition, have a lot of intervention property or biopsy procedure, wherein the imaging data of at first former collection is concentrated and is determined the pathology position.When this program of execution, by aiming at the placement that outside boundary mark is finished intervention property equipment (for example radio frequency ablation needle, biopsy needle etc.) according to the data set of collecting in advance.May reduce the accuracy of the placement of intervention property equipment with the incoherent motion of external label (such as being derived from respiratory movement, normally beat the heart movement under the pattern and the metallaxis of other motors).
A lot of these clinical problems can solve by the intravital motion of abundant detection body.
Past has used Several Methods to detect the intravital motion of body.In order to proofread and correct respiratory movement, sometimes pressure transducer is used in the suspender belt (halter) that affixes to the patient thoracic cavity to measure breathing rate.The perspective model of prediction position, patient thoracic cavity can be used to proofread and correct this motion then.
Simultaneously, sound wave (especially comprising ultrasonic) can be used for a lot of science or technical field, such as the harmless control of medical diagnosis, mechanical part and imaging under water etc.Sound wave can be diagnosed and controls as replenishing of optical observation, because sound wave can advanced in the opaque medium to electromagnetic wave.
Therefore, ultrasonic translational motion and the distortion that has been proposed for the measurement internal is because it can sensing deep structure and corresponding motion thereof.Work out some solutions to more complicated based on imaging method from the simple single element transducer under Doppler or the M pattern.Under the situation of single element sonic transducer, the ability that usually detects motion is only along the direction of sonic propagation line.This only allows to measure limited visual field.In this case, in order to detect real distortion and three-dimensional motion, may need a plurality of pick offs.
Acoustic imaging equipment with a plurality of pick offs comprises the equipment that utilizes traditional one dimension (" 1D ") acoustic transducer array, and the equipment that utilizes full sampling two dimension (" the 2D ") acoustic transducer array that adopts the microbeam forming technique.
In the equipment that utilizes the 1D acoustic transducer array, often arrange in one way that acoustic transducer element is to optimize the focusing in single plane.This allows to go up in axially dimension (being the direction of propagation) and the transverse dimensions direction of 1D array (promptly along) and focuses on the acoustic pressure wave launching and received.Usually the geometry by sonic transducer fixes (elevation angle) focusing outside the plane, and promptly the elevation angle of acoustic transducer element (elevation) highly controls the natural focal length of array on elevation dimension.For most of medical applications, only can be by increasing fixed lens in the acoustic transducer array front to focus on most of acoustic energy at the nominal depth of focus or to change (elevation angle) focal length outside the plane by changing the geometry of element on elevation.Unfortunately, this compromise often causes the suboptimum elevation angle at different depth place to focus on.
In each of these solutions, may expect to be increased in the ability of handling ultrasonic beam on the direction that existing transducer geometry can not realize.
Therefore, may expect to provide a kind of actual and cost-effective method of using sound wave to come the motion in the human body.Particularly, use electric controlled lens combination of forming by ultrasonic compatible fluids condenser lens and the transducer of uniting single or low parts number so that can detect motion with simple low cost solution.Further expectation provides a kind of device that uses sound wave to detect the intravital motion of body, but it needs less electronic equipment, less elements, and uses more cheap than existing apparatus potentially.
In one aspect of the invention, a kind of system that is used to detect the intravital motion of body comprises sonic probe, MEC, variable voltage source and controller.Described sonic probe comprises sonic transducer and is coupled to the variable refraction acoustic lens of described sonic transducer.Described variable refraction acoustic lens has pair of electrodes at least, and described variable refraction acoustic lens is suitable for regulating in response to the selection voltage that applies at the electrode two ends at least one characteristic of described variable refraction acoustic lens.Described MEC is coupled to described sonic transducer, and is suitable for execution algorithm to come the motion of detected object in response to the acoustic energy that is received by described sonic transducer.Described variable voltage source applies selection voltage to described counter electrode.Described controller is controlled described variable voltage source to apply described selection voltage to described counter electrode.
In another aspect of this invention, a kind of method of utilizing sound wave to detect motion comprises: (1) is applied to health with sonic probe; (2) the variable refraction acoustic lens of the described sonic probe of control is to detect the acoustic energy from the target area of described health; (3) be received from the sound wave that described target area is returned at the sonic transducer place from described variable refraction acoustic lens; (4) from the described sonic transducer output and the corresponding signal of telecommunication of sound wave that is received; (5) produce the sound data that receive according to the described signal of telecommunication by described transducer output; And (6) determine whether to focus on another target area of described health; (7) when selecting another target area, at the target area repeating step (1) of the new selection of institute to (6); And (8) handle sound data that received and one or more images of exporting the intravital motion of the described body of indication when no longer select target is regional.
Figure 1A-B illustrates an embodiment of the sonic probe that comprises the variable refraction acoustic lens that is coupled to sonic transducer;
Fig. 2 illustrates the block diagram of the embodiment of acoustic imaging device;
Fig. 3 illustrates the flow chart of an embodiment of the method for guide sound imaging device.
Now will be hereinafter by coming more fully to describe the present invention with reference to the accompanying drawings, the preferred embodiments of the present invention shown in the drawings.Yet the present invention can be presented as different forms and be not to be read as and be confined to embodiment as herein described.On the contrary, provide these embodiment as instruction example of the present invention.
As used herein, term " sound " refers to the operation of being undertaken by sound wave or undertaken by sound wave, and described sound wave especially comprises the ultrasound wave of frequency more than people's normal good hearing scope.In the following discussion, acoustic imaging device and the sonic probe that comprises variable refraction acoustic lens have been described.In the background of employed in this application term " variable refraction acoustic lens ", word " lens " is broadly defined as the equipment that is used for guiding or focuses on the radiation (especially acoustic radiation, for example ultrasonic radiation) that (may comprise light) except light.Though variable refraction acoustic lens can focused sound waves, the use of word in this background " lens " does not hint this focusing.Usually, the employed variable refraction acoustic lens of this paper is suitable for reflecting sound wave, and it can deflection and/or focused sound waves.
The variable focus fluid lens technology is to be initially scheme that special purpose that the variation that allows the physical boundary that would be filled with fluidic chamber of light by having specific refractive index is focused invents (referring to the open WO2003/069380 of Patent Cooperation Treaty (PCT), its full content is herein incorporated by reference, as it is put down in writing herein fully).The process that is called as " electric moistening " has realized the motion of flow surface, wherein comes the indoor fluid of mobile cavity by apply voltage at the conductive electrode two ends.The variation of this surface topology allows light to be refracted in such a way so that change travel path, thereby this light is focused on.
Simultaneously, ultrasonicly in fluid media (medium), propagate.In fact human body often is called as the fluid that can not carry the high frequency sound wave except compressional wave.On this meaning, these ripples are to deformation sensitive, and this distortion is caused by the velocity of sound difference of propagating in bulk tissue, and caused at the interface rapid variation by the velocity of sound.Adopted this characteristic among the embodiment of disclosed below sonic probe harmony imaging device.
Figure 1A-B illustrates an embodiment of the sonic probe 100 that comprises the variable refraction acoustic lens 10 that is coupled to sonic transducer 20.Variable refraction acoustic lens 10 is suitable for selecting voltage to regulate its at least one acoustical signal treatment characteristic in response at least one that it is applied.For example, variable refraction acoustic lens 10 comprises change that useful is is along propagating axis (" focusing ") and/or perpendicular to the ability of the elevation angle focal length of the sound wave of this plane (" deflection "), this is described in greater detail below.Variable refraction acoustic lens 10 comprises shell 110, coupling element 120, first fluid medium 141 and second fluid media (medium) 142, first electrode 150 and at least one second electrode 160a.For example, shell 110 can be columniform.Useful is, the top of shell 110 and bottom substantially transparent on acoustics, and sound wave does not penetrate shell 110 (a plurality of) sidewall.The bottom that sonic transducer 20 is coupled to shell 110 by one or more acoustic matching layers 130 valuably.
Sonic transducer 20 is the well-known types of art of acoustic waves.Useful is that sonic transducer 20 comprises the acoustic transducer element of 1D array, yet can use single element of transducer to replace the 1D array in certain embodiments.
In one embodiment, sonic probe 100 is suitable for operating under emission mode and receiving mode.For this situation, under emission mode, sonic transducer 20 will become the sound wave of its output to the electrical signal conversion of its input.Under receiving mode, sonic transducer 20 converts the sound wave of its reception to the signal of telecommunication of its output.
In alternative embodiment, sonic probe 100 can change into and be suitable for only operating under the receiving mode.In this case, provide transmitting transducer discretely.
Useful is, provides coupling element 120 at an end of shell 110.Coupling element 120 is designed to show contact area when compressing health (such as human body).Useful is, coupling element 120 comprises the elastic packing bag that is filled with the coupling solid content such as Mylar thin film (i.e. window) or has the plastic foil of the acoustic impedance that equates substantially with health.
Advantageously, the velocity of sound in the first fluid medium 141 and second fluid media (medium) 142 differ from one another (being that the speed that sound wave is propagated in fluid media (medium) 141 is different from the speed that it is propagated in fluid media (medium) 142).Equally, the first fluid medium 141 and second fluid media (medium) 142 are difficult for mixing each other.Therefore they always remain isolating fluid phase in chamber.Separation between the first fluid medium 141 and second fluid media (medium) 142 is contact surface or meniscus, and it limits the border between the first fluid medium 141 and second fluid media (medium) 142, and without any need for solid components.Equally advantageously, a kind of conduction in two kinds of fluid media (medium)s 141,142, and another kind is nonconducting substantially, or electric insulation.
In one embodiment, first fluid medium 141 mainly is made of water.For example, it can be a saline solution, and its ion concentration is enough high having the electric polarity performance, or conduction.In this case, first fluid medium 141 can comprise potassium ion and chloride ion, and the concentration of the two is for example 1mol.l
-1As an alternative, it can be water and alcoholic acid mixture, and (for example concentration is 0.1mol.l owing to the ion such as sodium ion or potassium ion for it
-1) existence and have sufficient electric conductivity.Second fluid media (medium) 142 for example can comprise the insensitive silicone oil of electric field.Following table 1 is listed can be as some exemplary fluid of the first fluid medium 141 or second fluid media (medium) 142.
Table 1
| Fluid | Density (g/cm 3) | The velocity of sound (km/s) | Decay under the 5MHz (dB/cm) |
| CCl 4 | 1.60 | 0.93 | 0.14 |
| Chlorobenzene | 1.1 | 1.3 | |
| Decahydronaphthalenes | 0.89 | 1.424 | 0.38 |
| Tetrahydronaphthalene | 0.97 | 1.468 | 0.12 |
| Phenylating silicone oil | 1.1 | 1.37 | 0.4 |
| Water | 1 | 1.5 | 0 |
| Methanol | 0.79 | 1.09 | 0.026 |
| Ethylene glycol | 1.11 | 1.689 | 0.31 |
| The perhydrogenate fluorenes | 0.92 | 1.4 |
Useful is that in the example of Figure 1A-B, when fluid media (medium) 141 mainly was made of water, the diapire of shell 110 was coated with hydrophilic coating 170 at least.Certainly, in different examples, when fluid media (medium) 142 mainly was made of water, the roof that can change shell 110 into was coated with hydrophilic coating 170.
Useful is, first electrode 150 is provided in the shell 110, so as with two kinds of fluid media (medium)s 141,142 in a kind of the contacting of conduction.In the example of Figure 1A-B, suppose that fluid media (medium) 141 is conducting fluids media, and fluid media (medium) 142 is nonconducting substantially fluid media (medium)s.Yet should be appreciated that fluid media (medium) 141 can be nonconducting substantially fluid media (medium), and fluid media (medium) 142 can be the conducting fluids medium.In this case, first electrode 150 can be arranged to fluid media (medium) 142 and contact.Equally in this case, the concavity of the contact meniscus shown in Figure 1A-B can be reversed.
Simultaneously, the sidewall along shell 110 provides the second electrode 160a.Randomly, (a plurality of) sidewall along shell 110 provides two or more electrodes 160a, 160b etc.Electrode 150 and 160a are connected to two outputs of variable voltage source (not shown among Figure 1A-B).
In operation, variable refraction acoustic lens 10 is operated in conjunction with acoustical convertor 20 as follows.In the exemplary embodiment of Figure 1A, when being applied to voltage between electrode 150 and the 160a by variable voltage source and being zero, the contact surface between the first fluid medium 141 and second fluid media (medium) 142 is meniscus M1.In known manner, the characteristic of the inner surface characteristic of the sidewall by shell 110 and the first fluid medium 141 and second fluid media (medium) 142 is determined the shape of meniscus.Its shape approximation is the part of sphere, especially has the situation of the density that equates substantially for the first fluid medium 141 and second fluid media (medium) 142.Because sound wave W has different spread speeds in first fluid medium 141 and second fluid media (medium) 142, the volume V that is filled with the first fluid medium 141 and second fluid media (medium) 142 plays the effect of lens concerning sound wave W.Therefore, enter probe 100 sound wave W pass between first fluid medium 141 and second fluid media (medium) 142 contact surface afterwards divergence change.The focal length of variable refraction acoustic lens 10 is the distances from sonic transducer 20 to the sound wave source point, thus this sound wave before striking on the sonic transducer 20 by variable refraction acoustic lens 20 complanation types.
When be applied to by variable voltage source voltage between electrode 150 and the 160a be set on the occasion of or during negative value, the shape of meniscus is owing to the electric field between electrode 150 and the 160a changes.Particularly, on the part of the contact surface between the first fluid medium 141 contiguous first fluid media 141 and second fluid media (medium) 142, apply active force.Because the polar behavior of first fluid medium 141, it be easy to according to the polarity of the voltage that is applied and fluidic relative surface tension move more close electrode 160a or further from electrode 160a.In the example of Figure 1B, M2 represents the shape of contact surface when voltage is set to nonzero value.This automatically controlled variation of contact surface form is called as electric moistening.Under the situation of first fluid medium 141 conduction, the change of shape of the contact surface when applying voltage between first fluid medium 141 and second fluid media (medium) 142 and previously described identical.Because the variation of contact surface form, the signal processing characteristic of variable refraction acoustic lens 10 changes during for non-zero at voltage.
The open WO2004051323 of PCT provides the detailed description about the meniscus of the variable refraction fluid lens that tilts, and the full content of the disclosure is herein incorporated by reference, as it is put down in writing herein fully.
Fig. 2 is to use the sonic probe that comprises the variable refraction acoustic lens that is coupled to sonic transducer to come the block diagram of the embodiment of the ultrasonic motion detection system 200 of motion in the detection bodies.Ultrasonic motion detection system 200 comprises processor/controller 210, transmiting signal source 220, transmit/receive switch 230, sonic probe 240, wave filter 250, gain/attenuator level 260, MEC 270 and variable voltage source 290.Simultaneously, sonic probe 240 comprises the variable refraction acoustic lens 242 that is coupled to sonic transducer 244.
Sonic probe 240 can be implemented as sonic probe 100, as top described about Fig. 1.In this case, useful is but that two kinds of fluids 141,142 of variable refraction acoustic lens 242 have impedance for matching have the different velocities of sound.This will allow the maximum of sound wave to propagate forward, allow the direction of control wave beam simultaneously.Useful is, fluid 141,142 has and is chosen as the focusing that makes sound wave and the velocity of sound of refractive maximum flexibility.
Useful is, acoustic transducer element 244 comprises the acoustic transducer element of one-dimensional array, although in alternative embodiment, it can comprise single element of transducer.
In operation, ultrasonic motion detection system 200 following operations.
Processor/controller 210 control is applied to the voltage on the electrode of variable refraction acoustic lens 242 by variable voltage source 290.As explained above, this so that changed the refraction of variable refraction acoustic lens 242.
When the falcate surface that is limited by two kinds of fluids in the variable refraction acoustic lens 242 reaches correct topological structure, processor/controller 210 control transmiting signal sources 220 are to generate the signal of telecommunication of expectation, and the signal of telecommunication of this expectation will be applied to sonic transducer 244 to generate the sound wave of expectation.In one case, can control transmiting signal source 220 to be created on (broadband) in short-term signal of operating under the M pattern, it might be that short burst sound is listed as other coherent signals to allow impulse wave Doppler or to be used for other imaging techniques.Typical purposes may be that imaging is carried out on the plane of the fixed elevation focal length with the region of clinical interest of being adjusted to.Acoustical signal can be the signal that time domain is differentiated, such as normal echo, M pattern or PW Doppler, perhaps even be the signal that non-time domain is differentiated, such as CW Doppler.Another typical purposes may be to regulate the focal length of ultrasonic transducer so that the signal maximization that is associated with histokinesis.
Useful is that processor/controller 210 execution algorithms are so that at enough short interval interscan volume (for example next plane), to differentiate the motion that takes place in this volume.That is to say, the energy that is applied to sonic transducer 244 by suitable control is with the ripple at the top of one's voice of going out to drill at least one direction, and the contact potential series of suitably controlling the electrode that is applied to variable refraction acoustic lens 242 obtains to be used for the data of three-D volumes view to control the refraction of sound wave on second direction and/or the depth of focus of sound wave thus.To pass to MEC 270 by the sound data that a series of measurements at Different Plane and/or degree of depth place receive by sonic probe 240.The sound data that MEC 270 processing receive are to produce image and/or other output, thereby express or illustrate the motion in the zone of being scanned by ultrasonic motion detection system 200, such as breath cycle, heart movement or the kinetic motion of patient's muscular tissue by the patient.
In the embodiment of Fig. 2, sonic probe 240 is suitable for emission mode and receiving mode operation.As explained above, in alternative embodiment, sonic probe 240 can change into and be suitable for only operating under the receiving mode.In this case, provide transmitting transducer discretely, and can omit transmit/receive switch 230.
Fig. 3 illustrates the flow chart of an embodiment of the method for operating 300 of controlling ultrasonic motion detection system 200.
At first step 305, sonic probe 240 is coupled to the patient.
Then, in step 310, processor/controller 210 control is applied to the voltage on the electrode of variable refraction acoustic lens 242 by variable voltage source 290, to begin to scan the volumetric region of expectation.
Then, in step 315, processor/controller 210 control transmiting signal sources 220 and transmit/receive switch 230 with the signal of telecommunication that applies (a plurality of) expectation to sonic transducer 244.Variable refraction acoustic lens 242 is operated to generate sound wave and with this sound wave deflection and/or focus in patient's the target area with sonic transducer 244.
Subsequently, in step 320, variable refraction acoustic lens 242 is operated the sound wave that returns from patient's target area to receive with sonic transducer 244.At this moment, processor/controller 210 control transmit/receive switch 230 are to be connected to sonic transducer 244 in wave filter 250 to export (a plurality of) signals of telecommunication to wave filter 250 from sonic transducer 244.
Then, in step 330, wave filter 250, gain/attenuator level 260 and acoustic signal processor 270 are operated together adjusting the signal of telecommunication from sonic transducer 244, and produce the sound data that receive in view of the above.
Then, in step 340, the sound data that receive are stored in the memorizer (not shown) of MEC 270 of ultrasonic motion detection system 200.
Next, in step 345, processor/controller 210 determines whether at other direction, the degree of depth and/or plane inner focusing.If like this, then select scanning area in step 350, and in step 310 process repeats.If not so, handle at step 355 MEC 270 then that the sound data (possible associated processors/controller 210) that receive express or illustrate the image of the motion in scanned by ultrasonic motion detection system 200 regional with generation and/or other are exported, described motion is for example by patient's breath cycle, heart movement or the kinetic motion of patient's muscular tissue.
At last, in step 360, image and/or other output of the motion that ultrasonic motion detection system 200 output expressions are detected.
Though disclose preferred embodiment at this, a lot of variations are still possible in notion of the present invention and scope.For those of ordinary skills, after description, accompanying drawing and claims of checking herein, these variations will become apparent.Therefore the restriction of the spirit and scope of the present invention's claim of only being enclosed.
Claims (15)
1, a kind of system (200) that is used to detect the intravital motion of body, it comprises:
Sonic probe (240,100), it comprises,
Sonic transducer (244,20) and
Be coupled to described sonic transducer (244,20) variable refraction acoustic lens (242,10), described variable refraction acoustic lens (242,10) has pair of electrodes (150 at least, 160a, 160b), described variable refraction acoustic lens be suitable in response to described electrode (150,160a, 160b) the selection voltage that applies of two ends at least one characteristic of regulating described variable refraction acoustic lens (242,10);
MEC (270), it is coupled to described sonic transducer (244,20), and is suitable for the motion of execution algorithm to come detected object in response to the acoustic energy that is received by described sonic transducer (244,20);
Variable voltage source (290), it is suitable for, and (150,160a 160b) applies selection voltage to described counter electrode; And
Controller, it is suitable for controlling described variable voltage source (290) so that (150,160a 160b) applies described selection voltage to described counter electrode.
2, the system as claimed in claim 1 (200), it also comprises:
Transmiting signal source (220); With
Transmit/receive switch (230), it is suitable for optionally described sonic transducer (244,20) being coupled to described transmiting signal source (220) and being coupled to described MEC (270).
3, the system as claimed in claim 1 (200), wherein, described variable refraction acoustic lens (242,10) comprising:
Chamber;
Be arranged on first fluid medium (141) and second fluid media (medium) (142) in the described chamber; And
First and second electrodes (150,160a, 160b),
Wherein, the velocity of sound of sound wave in described first fluid medium (141) is different from the corresponding velocity of sound of described sound wave in described second fluid media (medium) (142),
Wherein, described first fluid medium (141) and described second fluid media (medium) (142) can not mix each other, and
Wherein, described first fluid medium (141) has and the different substantially electrical conductivity of described second fluid media (medium) (142).
4, system as claimed in claim 3 (200), wherein, described first fluid medium (141) and described second fluid media (medium) (142) have the basic density that equates.
5, system as claimed in claim 3 (200), wherein, described variable refraction acoustic lens (242,10) comprise the shell (110) that limits described chamber, and wherein, in the described counter electrode first (150) is set on the bottom or top of described shell (110), and in the described counter electrode second (160a 160b) is set on the sidewall of described shell (110).
6, system as claimed in claim 3 (200), wherein, in the described counter electrode first (150) be set to described first fluid medium and described second fluid media (medium) in have big electrical conductivity a kind of (141) contact, and (160a is 160b) with to have a kind of (142) of big electrical conductivity isolated in described first fluid medium and described second fluid media (medium) in the described counter electrode second.
7, the system as claimed in claim 1 (200), wherein, described variable refraction acoustic lens (242,10) is coupled to described sonic transducer (244,20) by at least one acoustic matching layer (130).
8, the system as claimed in claim 1 (200), wherein, in response at described electrode (150,160a, 160b) the described selection voltage that applies of two ends and the described variable refraction acoustic lens (242 that is conditioned, 10) described at least one characteristic comprises the focal length and the elevation angle of described variable refraction acoustic lens (242,10).
9, a kind of method (300) of utilizing sound wave to detect motion, described method comprises:
(1) sonic probe is applied to health (305);
(2) the variable refraction acoustic lens of the described sonic probe of control is to detect the acoustic energy (310) from the target area of described health;
(3) be received from the sound wave (320) that returns described target area at the sonic transducer place from described variable refraction acoustic lens;
(4) from the described sonic transducer output and the corresponding signal of telecommunication of sound wave that is received;
(5) produce the sound data (330) that receive according to the described signal of telecommunication by described transducer output; And
(6) determine whether to focus on another target area (345) of described health;
(7) when selecting another target area, at the target area repeating step (1) of new selection to (6); And
(8) when no longer select target is regional, handle sound data (355) that received and one or more images (360) of exporting the intravital motion of the described body of indication.
10, method as claimed in claim 9 (300), it also comprises the sound data storage (340) in memorizer that will be received.
11, method as claimed in claim 9 (300), it also is included in step (3) and before the signal of telecommunication is applied to the described sonic transducer that is coupled to described variable refraction acoustic lens, to generate sound wave and described sound wave is directed to described target area (315).
12, method as claimed in claim 9 (300), wherein, control described variable refraction acoustic lens to detect acoustic energy (310) from the target area of described health, comprise apply voltage to the electrode of described variable refraction acoustic lens so that two kinds of fluids in the shell that is arranged on described variable refraction acoustic lens are shifted each other, wherein, described two kinds of fluids have different acoustic wave propagation velocities each other.
13, method as claimed in claim 9 (300) wherein, is controlled described variable refraction acoustic lens to detect the acoustic energy (310) from the target area of described health, comprises at least one the signal processing characteristic that changes described variable refraction acoustic lens.
14, method as claimed in claim 13 (300), wherein, described at least one signal processing characteristic that is conditioned of described variable refraction acoustic lens is the focal length of described variable refraction acoustic lens.
15, method as claimed in claim 13 (300), wherein, described at least one signal processing characteristic that is conditioned of described variable refraction acoustic lens is the deflection angle of described variable refraction acoustic lens.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US88641107P | 2007-01-24 | 2007-01-24 | |
| US60/886,411 | 2007-01-24 |
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| Publication Number | Publication Date |
|---|---|
| CN101600392A true CN101600392A (en) | 2009-12-09 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNA2008800029144A Pending CN101600392A (en) | 2007-01-24 | 2008-01-18 | Use adjustable fluid lenses motion to be carried out the method and apparatus of ultrasound detection |
Country Status (4)
| Country | Link |
|---|---|
| EP (1) | EP2124754A1 (en) |
| JP (1) | JP2010516372A (en) |
| CN (1) | CN101600392A (en) |
| WO (1) | WO2008090504A1 (en) |
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| CN105662465A (en) * | 2016-01-11 | 2016-06-15 | 飞依诺科技(苏州)有限公司 | Ultrasonic probe and ultrasonic testing method |
| CN105748106A (en) * | 2016-04-22 | 2016-07-13 | 毛军卫 | Ultrasonic probe and ultrasonic detection equipment with same |
| CN106037663A (en) * | 2016-06-29 | 2016-10-26 | 华南师范大学 | Continuous zooming ultrasonic probe and zooming method adopted by same |
| CN107356918A (en) * | 2017-07-10 | 2017-11-17 | 苏州优函信息科技有限公司 | Millimetre-wave radar based on the continuous millimeter wave in face and receiving array sensor |
| CN108697404A (en) * | 2016-02-12 | 2018-10-23 | 高通股份有限公司 | Ultrasonic equipment for estimated blood pressure and other cardiovascular properties |
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| CN102170938B (en) * | 2008-09-30 | 2015-01-14 | 皇家飞利浦电子股份有限公司 | System and method for ultrasound therapy treatment |
| JP2012516182A (en) | 2009-01-30 | 2012-07-19 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Acoustic device for ultrasound imaging |
| CN102326093A (en) * | 2009-02-20 | 2012-01-18 | 皇家飞利浦电子股份有限公司 | Utilize the ultrasonic imaging of changeable refractive index lens |
| CN103827960B (en) | 2011-09-26 | 2017-12-08 | 皇家飞利浦有限公司 | Ultrasonic probe with acoustic lens |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE3120611A1 (en) * | 1981-05-23 | 1982-12-16 | Battelle-Institut E.V., 6000 Frankfurt | Device for radiating and for receiving focused ultrasonic waves |
| US5285788A (en) * | 1992-10-16 | 1994-02-15 | Acuson Corporation | Ultrasonic tissue imaging method and apparatus with doppler velocity and acceleration processing |
| US5669385A (en) * | 1996-03-13 | 1997-09-23 | Advanced Technology Laboratories, Inc. | Ultrasonic scanning of tissue motion in three dimensions |
| US6589176B2 (en) * | 2001-12-05 | 2003-07-08 | Koninklijke Philips Electronics N.V. | Ultrasonic image stabilization system and method |
| JP4564850B2 (en) * | 2002-12-03 | 2010-10-20 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Apparatus for forming variable fluid meniscus structure |
| US20080264716A1 (en) * | 2004-06-07 | 2008-10-30 | Koninklijke Philips Electronics N.V. | Acoustic Device With Variable Focal Length |
-
2008
- 2008-01-18 EP EP08702468A patent/EP2124754A1/en not_active Withdrawn
- 2008-01-18 JP JP2009546847A patent/JP2010516372A/en not_active Withdrawn
- 2008-01-18 WO PCT/IB2008/050194 patent/WO2008090504A1/en active Application Filing
- 2008-01-18 CN CNA2008800029144A patent/CN101600392A/en active Pending
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Also Published As
| Publication number | Publication date |
|---|---|
| EP2124754A1 (en) | 2009-12-02 |
| JP2010516372A (en) | 2010-05-20 |
| WO2008090504A1 (en) | 2008-07-31 |
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