CN1287741C - Transesophageal and transnasal, transesophageal ultrasound imaging systems - Google Patents

Transesophageal and transnasal, transesophageal ultrasound imaging systems Download PDF

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Publication number
CN1287741C
CN1287741C CNB028030826A CN02803082A CN1287741C CN 1287741 C CN1287741 C CN 1287741C CN B028030826 A CNB028030826 A CN B028030826A CN 02803082 A CN02803082 A CN 02803082A CN 1287741 C CN1287741 C CN 1287741C
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image
imaging system
data
probe
transesophageal
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CN1476311A (en
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D·G·米勒
M·佩斯茨恩斯基
H·贝克
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Koninklijke Philips NV
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Koninklijke Philips Electronics NV
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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
    • A61B8/12—Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
    • A61B8/445—Details of catheter construction
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
    • A61B8/4488—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer the transducer being a phased array
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/8927—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array using simultaneously or sequentially two or more subarrays or subapertures
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
    • A61B8/4494—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer characterised by the arrangement of the transducer elements
    • 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
    • A61B8/483—Diagnostic techniques involving the acquisition of a 3D volume of data

Abstract

A semi-invasive ultrasound imaging system for imaging biological tissue includes a transesophageal probe or a transnasal, transesophageal probe connected to a two-dimensional ultrasound transducer array, a transmit beamformer, a receive beamformer, and an image generator. The two-dimensional transducer array is disposed on a distal portion of the probe's elongated body. The transmit beamformer is connected to the transducer array and is constructed to transmit several ultrasound beams over a selected pattern defined by azimuthal and elevation orientations. The receive beamformer is connected to the transducer array and is constructed to acquire ultrasound data from the echoes reflected over a selected tissue volume. The tissue volume is defined by the azimuthal and elevation orientations and a selected scan range. The receive beamformer is constructed to synthesize image data from the acquired ultrasound data. The image generator is constructed to receive the image data and generate images that are displayed on an image display. Preferably, the image generator is constructed to generate, from the image data, several orthographic projection views over the selected tissue volume.

Description

The ultrasonic image-forming system of transesophageal and per nasal, esophagus
The present invention relates to half intrusive mood ultrasonic image-forming system, the ultrasonic image-forming system of transesophageal ultrasonic image-forming system that several 2 d plane pictures and being used to manifest the projection of 3 D anatomy structure in patient's body and per nasal, esophagus particularly can be provided.
Non-intrusion type, half intrusive mood and intrusive mood ultrasonic image-forming system have been widely used in the intravital organizational structure of observer, such as cardiac structure, abdomen organ, fetus and vascular system.Half intrusive mood system comprises transesophageal ultrasonic image-forming system, and the intrusive mood system comprises imaging system in the vascular.According to the type and the position of tissue, different systems can obtain or provide the visual field of better internal physiological tissue better.
In general, ultrasonic image-forming system comprises the transducer array that links to each other with the received beam maker with multichannel transmission wave beam.Send beamformer and electric pulse is offered each transducer, to generate the transmission wave beam of propagating from array along predetermined direction with predetermined sequential.When sending wave beam by health, part acoustic energy is reflected back to transducer array from the organizational structure with different acoustic characteristics.Receiving transducer (can be the transmission transducer with receiving mode work) converts the pressure pulse that is reflected to corresponding electric RF (radio frequency) signal that is provided for the received beam maker.Because the different distance from pip to each transducer, the sound wave that is reflected reaches each transducer with the different time, and like this, RF (radio frequency) signal has different phase places.
The received beam maker has a plurality of processing channels, handles channel and has the compensating delay element that links to each other with adder.The received beam maker selects to be used for the length of delay of each channel, so that in conjunction with the echo from selected focus reflection.Therefore, when inhibit signal is summed, produce strong signal by signal corresponding to this point.But the signal that comes from difference has the random phase relation corresponding to the different time, thereby disturbs devastatingly.The received beam maker is selected to control the such relative delay of received beam with respect to the orientation of transducer array.Like this, the received beam maker is dynamically controlled received beam so that have required orientation, and they are focused on.Therefore, ultrasonic system obtains acoustic data.
For the Real Time Observation organizational structure, used various ultrasonic systems to produce the two and three dimensions image.Conventional ultrasonic image-forming system obtains the two dimensional image plane perpendicular to the surface of the transducer array that acts on patient body.In order to produce 3-D view, ultrasonic system must obtain acoustic data on three-D volumes, for example by making one dimension (perhaps one dimension half) transducer array move through several position.Perhaps, two-dimensional transducer array can obtain the scan-data on a plurality of planes of delineation.Under each situation, this system's memory image panel data is with reconstruction of three-dimensional images.But in order to make the movable organ imaging such as heart, it is important obtaining data apace and generating image as quickly as possible.This needs the fast processing of high frame frequency (that is the amount of images of unit interval generation) and view data.But spacescan (for example, when one-dimensional array is moved through several position) is not instantaneous.Like this, when making movable organ imaging, the interference of tangling mutually of time dimension and three Spatial Dimensions.
Several ultrasonic systems have utilized that data are obtained, volume reconstruction and image manifest and generate 3D (three-dimensional) image.A kind of ultrasonic system of routine utilizes transducer probe scan patients destination organization and receives a plurality of Frames and obtains data.This system is with respect to frame, reference frame or reference position draw the position of each frame and be orientated indication the preceding.Then, this system with the corresponding indication of frame data and each frame as the input that manifests process for volume reconstruction and image.This 3D ultrasonic system carries out volume reconstruction by limiting a reference frame, and each picture frame is arranged in this reference frame with the sequence of the picture frame of record.Reference frame is the coordinate system that is used to comprise the planar 3D volume of all images that is used to generate 3D rendering.First picture frame is used to limit reference frame (thereby limiting the 3D volume), and reference frame has three spherical coordinate axle (r v, θ vAnd  vSpool) or three orthogonal axis (that is x, v, y vAnd z vAxle).Each picture frame is to have two polar axis shaft (that is r, iAnd θ iSpool) or two orthogonal axis (that is x, iAnd y i) 2D section (that is, plane picture), wherein i is an i picture frame.Like this, each sample point in a plane of delineation has plane of delineation coordinate in the plane of delineation coordinate system that is used for such plane of delineation.In order to write down sample in reference frame, the sample point coordinates in the plane of delineation coordinate system that is fit to is transformed in the reference frame.If a plane of delineation sample does not appear at the specific rounded coordinate place of reference frame, this system carries out interpolation so, with distribution diagram between nearest reference coordinate mooring points as planar sample.
For storing sample data or the interpolation that draws by sample data, this system assignment memory address space, wherein memorizer can be mapped to reference frame.A given row's of like this, given reference volume section numerical value (for example obtaining along the z axle) can be stored in the sequence addressed location.In addition, the numerical value of the adjacent row in such section can be stored in the adjacent first memory address space.This system can increase progressively reconstruction by the transformation matrix that calculating comprises six offsets.Have (along this row of image) calculating x on the x direction, three offsets of y and z coordinate have at (under these row at image) on the y direction and calculate x, three offsets of y and z coordinate.Then, the bight of this system-computed reconstruct volume and they and the coordinate that defines volume compared.Next, this system determines the image that is obtained and defines the intersection of coordinate and image coordinate system is got back in their conversion.This can utilize several digital signal processors to finish.
In addition, the rectangular projection of the current state of reconstruct volume can be calculated by this system.Better simply draw calculation (need not to calculate interpolation to carry out being tied to from reference coordinate the transformation of display image raster coordinate system) is used in rectangular projection.This system can use maximum intensity projection (MIP) drafting method, wherein along the depth direction projection radiation of volume, and the maximum that is run into is the value of throwing for this ray (for example, being used to obtain the numerical value of the pixel of the given optical grating point on the 2D image projection).This system incrementally rebuilds and display-object volume in real time.Operator's object observing volume in real time improves shown image with the scanning effect and by repeatedly desired zone specially being scanned.The operator also can restart to carry out volume reconstruction in new visual angle.
As time goes on this image process for show obtains the 2D image projection of 3D volume with the generation rotating image or with new perspective generated image.This system uses and shears the new 2D projection that the distortion factorization method obtains one or more given video frame image.For each visual angle change, this method becomes to be parallel to the 3D shearing of the section of volume data with the necessary factorisation of viewing transformation matrix.The projection of shearing forms the 2D intermediate image.Can carry out 2D distortion producing final image, the 2D projection of the 3D volume at required visual angle (that is, with).This system uses final image sequence with different visual angles to produce the real-time revolved view of target volume.
Known other system only uses the power doppler image to eliminate a large amount of clutter echoes that produced by the structural information signal in three dimensional display.Such doppler system is stored in the image sequence memory with Doppler's power show value that the sequence of plane picture will have space coordinates.User can provide the processing parameter that comprises angular field of view.For example, user can be imported with at the angular field of view and the scope increment that are reference perpendicular to a sight line in the planar plane of first image in sequence.Calculate the tripleplane of requirement according to these inputs.Then, this system utilizes scan converter and video-stream processor to carry out the essential sequence that sequential processing forms maximum intensity projection by at first transferring plane Doppler's power diagram picture from image sequence memory again.Processor makes each plane picture turn to one of them is got back to viewing plane by projection visual angle.
The doppler system plane picture pixel that accumulation is projected based on maximum intensity.Each plane picture that is projected be coated on the previous cumulative projected image but in the transposition section in the plane of delineation, there are such functional relationship in this transposition section and visual angle and interplanar interval: the visual angle is big more, and an image is big more to the transposition displacement between the next image.The display pixel of from cumulative image, selecting be from each point in image cumulative all cover the maximum intensity pixel of each point of obtaining in pixels in the plane of delineation.This has showed the maximum intensity of viewer along the viewed Doppler's power of each sight line between viewer and the three dimensional display effectively.
This system is rotatable, projection, transposition, cover and be chosen in the maximum intensity at each pixel place of all plane pictures, then resulting three dimensional display for this visual angle is stored in the image sequence memory.Can transfer and show stored three-dimensional sequence according to the instruction of user.When transferring in real time and showing this sequence, user can be seen the action that occurs or the three dimensional display of fluid flow in obtaining the volumetric region of plane picture.Observe this volumetric region with three dimensional constitution, move around this zone and from the view action that changes or flow as user.Viewer can inswept back and forth this sequence, is given in the effect that moves around this volumetric region on both direction.
It also is known utilizing improved two-dimensional ultrasonic imaging system that three-dimensional ultrasound pattern is provided.Such three-dimension ultrasonic imaging system can use conventional ultra sonic imaging hardware and scan converter.The two-dimensional ultrasonic imaging system obtains a plurality of two dimensional images.This system handles image so that they rotate and reference plane are got back in projection by scan conversion on each plane of delineation, but reference plane initial pictures plane.Can use conventional scan conversion hardware to readjust the segment angle or the degree of depth of sector image, perhaps carry out the length-width ratio of image.This system is for a plurality of planes of each image projection and then store them with the sequence of composograph, and wherein each composograph comprises one group of respective projection image of setovering each other.Each composograph is the different views by the occupied 3D region of plane picture information.
Said system can playback composograph sequence just be rotated in the viewer front as 3D region to describe 3D region on display.In addition, this system can transfer based on three dimensional viewing perspective and the stored composograph that shows in proper order with the three-dimensional representation form.
The medical procedure that also is not extensive use of ultrasonic image-forming system has several.At present, for example the interference technique cardiologist mainly uses fluorescence imaging to guide and moves device in vascular system or heart.These processes are normally inserted in laboratory (Cathlab) or the electrophysiology lab (Eplab) at cardiac catheter and are carried out.In the cardiac catheter insertion process, fluoroscope is using X ray to think that the doctor provides the transmission diagram of the chest that comprises heart on the frame frequency in real time.Has each other the real-time Transmission image that cardiac structure is provided with the bi-planar fluoroscopic detector of two pairs of transmitter-receivers of 90 ° of installations.These images are owing to helping the location of doctor to each conduit for the doctor provides the sensation of the three-dimensional geometrical structure of heart.
Although fluoroscopy is a kind of otherwise effective technique, it can not provide the high quality graphic that has good contrast for soft tissue.In addition, doctor and medical assistance personnel must wear the lead protection clothes and must reduce the fluoroscopy time as much as possible to reduce the radiation of X ray to them.In addition, because harmful effect of X ray is out of use and make fluoroscopy for some patients, anemia of pregnant woman for example.In recent years, transthoracic and transesophageal ultra sonic imaging has been used for clinical and surgical operation very effectively, does not insert in laboratory and the electrophysiology lab but also be widely used for the cardiac catheter that the patient stands interference technique.
Therefore, need provide ultrasonic image-forming system and method through esophagus or per nasal, esophagus, it can provide fast and be applied to the realtime imaging of the cheapness of computer.Image should be able to manifest internal anatomy that comprises each structure and the selection view that the tissue of being paid close attention to is provided effectively.A kind of ultrasonic system and method for the real time imaging that anatomical structure accurately is provided and is convenient to understand can medically obtain other application.
The present invention relates to be used to make the 3 D anatomy structure imaging and/or make the transesophageal ultrasonic device or the method for the novelty that imports the intravital medical treatment device of patient (for example, therapy equipment, the diagnostic equipment, apparatus for correcting, intravascular stent) imaging.
According to an aspect, a kind of transesophageal ultrasonic image-forming system that is used for physiological tissue's imaging comprises: the transesophageal probe that links to each other with two-dimensional ultrasound transducer arrays; Send beamformer; The received beam maker; And image composer.Two-dimensional ultrasound transducer arrays is arranged on the distal portion of elongate body of probe.The transmission beamformer links to each other with transducer array and be configured to send a plurality of ultrasonic beams on the selection pattern that is limited by azimuthal orientation and absolute altitude orientation.The received beam maker links to each other with transducer array and is constructed to be permeable to and obtain ultrasound data from the echo that reflects in selected tissue volume.Tissue volume is by azimuthal orientation and absolute altitude is directed and selected sweep limits limits.The received beam maker is constructed to be permeable to come the composograph data by the ultrasound data that is obtained.Image composer is constructed to be permeable to receive view data, and generates and can go up the image that shows selected tissue volume at image display (video display units, printer etc.).
The preferred embodiment of this method comprises one or more of following feature:
Image composer is configured to generate at least two orthogonal projection figure about selected tissue volume by view data, and image display is configured to so that show described two projections at least.
Ultrasonic image-forming system can comprise surface detectors and processor controls.Surface detectors is configured to receive image parameter and generate surface data by view data from processor controls.Image composer is configured to generate the projected image that can be presented on the image display by surface data.
Surface detectors is the B-scan edge detector, and image composer is configured to generate the plane graph that comprises projected image by view data and surface data.In addition, image composer is configured to generate at least two orthogonal projection figure by view data and surface data, and each orthogonal projection figure comprises plane graph and projected image.Surface detectors can be the C-scan edge detector, and image composer is configured to generate C-scan figure.
Ultrasonic image-forming system is included as the probe of transesophageal probe or per nasal, esophagus.Transesophageal probe comprises the locking mechanism of jointly arranging with the attachment areas of probe, and described locking mechanism is configured to make the transducer array locks in place after array is with respect to the tissue regions orientation of being paid close attention to.The probe of per nasal, esophagus comprises the locking mechanism of jointly arranging with the attachment areas of probe, and described locking mechanism is configured to make the transducer array locks in place after array is with respect to the tissue regions orientation of being paid close attention to.
Transducer array and beamformer are configured to obtain ultrasound data with the pattern work of phased array and for several image sector that have specified absolute altitude position respectively on selected bearing range.Transducer array comprises a plurality of subarrays that link to each other with the received beam maker with transmission.
Image composer is configured to generate at least two orthogonal projection figure about selected tissue volume by view data, and image display is configured to show described at least two projections.Image composer is configured to generate as two orthogonal projection figure that just penetrating B-scan figure and generates an orthogonal projection figure as C-scan figure.
Transesophageal probe also can comprise the locking mechanism of jointly arranging with the attachment areas of probe, and described locking mechanism is configured to after array is with respect to the tissue regions orientation of being paid close attention to the transducer array locks in place.
Ultrasonic image-forming system comprises processor controls, and processor controls is configured to and is arranged to based on the transmission of range data control ultrasonic beam and synthesizing of control view data by user provided.Transducer array comprises a plurality of subarrays that can link to each other with the received beam maker with transmission, and processor controls is configured to control the layout of subarray so that obtaining of the echo data of tissue volume reaches best.Processor controls is constructed to and sends beamformer and the received beam maker provides sweep parameter, and described sweep parameter comprises the scanning ratio of imaging depth, frame frequency or azimuth and absolute altitude.
Processor controls is configured to receive the input data and dateout is provided, and makes to send and received beam maker change bearing range.Processor controls is configured to receive the input data and dateout is provided, and makes to send and received beam maker change absolute altitude scope.Processor controls is constructed to image composer provides data with by recomputating the deflection angle that orthogonal projection figure proofreaies and correct described figure.By changing bearing range or absolute altitude scope, the doctor can be on the less data volume of the center of the tissue of being paid close attention to boot scan.By scanning on smaller volume, this system improves the realtime imaging of active organization by improving frame frequency, and this is because it has collected less data point.
Image composer comprises at least one figure interpolation processing device and at least one icon maker, described figure interpolation processing device is configured to generate two orthogonal projection figure at least, described icon maker be configured to generate at least two with described at least two icons that orthogonal projection figure is relevant, and described image composer comprises at least one edge detector, and it is configured to and is arranged to detect organizational boundary.
Figure interpolation processing device is arranged to generate B-scan figure and C-scan figure, and C-scan figure generates by receiving the C-scan appointed information from B-scan figure.Figure interpolation processing device is an orientation diagram interpolation processing device.Figure interpolation processing device is an absolute altitude figure interpolation processing device.Figure interpolation processing device comprises the gating peak detector.
Edge detector is the B-scan edge detector, and the interpolation processing device also can be arranged to receive data with the border the outstanding orthogonal projection figure from the B-scan edge detector.Edge detector is the C-scan edge detector, and the interpolation processing device also can be arranged from the C-scan edge detector and receive data with the border the outstanding orthogonal projection figure.
Image composer comprises the deflection angle Correction Processor.Image composer comprises the scope processor, and described scope processor is configured to provide two scope pointers to be used to generate the C-scan projection.The scope processor is configured to receive the user input that limits these two scope pointers.The icon maker is configured to generate the orientation icon of display orientation angle range and the maximum azimuth coverage of demonstration.The icon maker is configured to show absolute altitude angle range and the absolute altitude icon that shows maximum absolute altitude angle range to generate.
According to another aspect, a kind of transesophageal ultrasonic imaging method carries out through the following steps: will import in the esophagus and with the selected orientation with respect to the tissue regions of being paid close attention to once the probe of esophagus and make the two-dimensional ultrasound transducer arrays location; On selected bearing range and selected position absolute altitude scope, ultrasonic beam is sent on a plurality of transmission scanning lines that come from transducer array; And the echo that reflects according to the selected tissue volume that is limited by bearing range, absolute altitude scope and the selected sector scanning degree of depth obtains the transducer array ultrasound data and comes composograph by the ultrasound data that is obtained.Next, generate image and show the image that is generated by the view data of selected tissue volume, thereby realize this ultrasonic imaging method.
Best, this transesophageal ultrasonic imaging method can comprise following one or more step: utilization can be obtained with the work of phased array pattern with in the bearing range of selecting about the transmission of the ultrasound data of the several image sector with known absolute altitude position and the step that the received beam maker sends and obtains.Generate step and be included at least two orthogonal projection figure of generation on the tissue volume, and step display comprises at least two orthogonal projection figure of demonstration.
This formation method can be used for operating theater instruments is positioned at the shown tissue place that is paid close attention to by orthogonal projection figure.Formation method is used in the position of examining operating theater instruments in the operation process based on orthogonal projection figure.Formation method can when utilizing operating theater instruments to undergo surgery, carry out orthogonal projection figure transmission, obtain, generate and show.This formation method can after utilizing operating theater instruments to undergo surgery, carry out orthogonal projection figure transmission, obtain, generate and show.
At least two orthogonal projection map generalizations can comprise the selected C-scan figure of generation.Selected C-scan map generalization can comprise the C-scan indication that is provided for selected C-scan figure.This indication can comprise a bottom view of qualification or limit a top view.The generation of C-scan can comprise and utilizes the C-scan edge detector to detect organizational boundary and utilize the gating peak detector to select ultrasound data for C-scan.
Formation method can be included as processor controls and the input data is provided and provide the dateout that comes from processor controls to send with guiding and received beam maker change bearing range.Formation method can be included as processor controls and the input data is provided and provide the dateout that comes from processor controls to send with guiding and received beam maker change absolute altitude scope.Processor controls also can be image composer provides data with by recomputating the deflection angle that orthogonal projection figure proofreaies and correct described figure.By changing bearing range or absolute altitude scope, the doctor can be on the less data volume of the center of the tissue of being paid close attention to boot scan.By the scanning smaller volume, this system improves the realtime imaging of active organization by improving frame frequency, and this is because it has collected less data point.
At least two orthogonal projection map generalizations can comprise the absolute altitude icon that generates the orientation icon relevant with maximum bearing range with selected bearing range or be correlated with selected absolute altitude scope and maximum absolute altitude scope.
Particularly, the present invention proposes a kind of transesophageal ultrasonography imaging system that is used for physiological tissue's imaging, it comprises the TEE probe, described TEE probe comprises: elongated half flexible body that has far-end, be connected to the flexure region of the far-end of described elongated half flexible body, be connected to the distal tip of the far-end of described flexure region, be connected to the probe handle of the near-end of described elongated half flexible body, described probe handle comprises the register control that is connected to described flexure region by described elongated half flexible body; With the matrix two-dimensional ultrasound transducer arrays that is in described distal tip; Described TEE probe is characterised in that described matrix two-dimensional ultrasound transducer arrays can be operated to the electronic guide wave beam on two planes more than volumetric region; Distal tip comprises the integrated circuit of the element that is connected to described two-dimensional ultrasound transducer arrays.
Distal tip also comprises the array backing of the element back that is positioned at described two-dimensional ultrasound transducer arrays.
Distal tip also comprises radiator, as the heat transfer effect of the heat that integrated circuit produced.
Elongated half flexible body comprises the gastroscope pipe.
Described probe comprises the locking mechanism of jointly arranging with the attachment areas of this probe, and described locking mechanism is configured to be locked in position in described two-dimensional ultrasound transducer arrays after described array is with respect to the tissue regions orientation of being paid close attention to.
The element of described two-dimensional ultrasound transducer arrays is set to two subarrays.
Receive preprocessor in also comprising a plurality of groups, each the described group interior preprocessor that receives links to each other with the element of subarray.
Receive in each group that preprocessor is configured to postpone and in conjunction with signal by the element of correlator array.
Also comprise parallel beamformer,, be arranged to synthetic simultaneously a plurality of received beams in response to the signal that the element by the matrix two-dimensional ultrasound transducer arrays receives.
Also comprise picture system,, be arranged in from the plane of delineation that extend on the plane of matrix two-dimensional ultrasound transducer arrays and produce one or more images in response to the signal that the element by the matrix two-dimensional ultrasound transducer arrays receives.
Described picture system works to produce a plurality of spaces different images; And also comprise orientation icon maker, be arranged to produce the display orientation icon of the relative orientation that shows described space different images.
Also comprise the picture system that is connected in described TEE probe, this picture system comprises the edge detector that is used for the signal that receives in response to the element by the matrix two-dimensional ultrasound transducer arrays.
Fig. 1 shows the ultrasonic system that comprises transesophageal imaging probe, and described transesophageal imaging probe comprises distal portions and half elongated flexible body.
Fig. 2 and Fig. 2 A are the schematic sectional view of the rigid region of transesophageal imaging probe.
Fig. 3 is the schematic sectional view with the attachment areas of the transesophageal probe of the form connection of the J hook in the plane.
Fig. 3 A is the schematic sectional view with the attachment areas of the transesophageal probe of the form connection of out-of-plane J hook.
Fig. 3 B is the schematic sectional view with the attachment areas of the transesophageal probe of the form connection of the S hook in the plane.
Fig. 3 C is the perspective view of coupling link that is used for the attachment areas of transesophageal probe.
Fig. 4 shows the scan volume of the echo data that is used to illustrate orthogonal projection figure.
Fig. 4 A, Fig. 4 B, Fig. 4 C, Fig. 4 D and Fig. 4 E show by with as be connected the different orientation of the scan volume that is generated in conjunction with the described distal portions of Fig. 3 to Fig. 3 B.
Fig. 5 shows the image composer of the ultrasonic system of Fig. 1 with the form of chart.
Fig. 5 A shows the processor controls of the ultrasonic system of Fig. 1 with the form of chart.
Fig. 5 B shows the ultrasound transducer array that links to each other with the received beam maker with the transmission beamformer of ultrasonic system with the form of chart.
Fig. 5 C shows the gating peak detector that is used in system shown in Fig. 5 with the form of chart.
Fig. 6, Fig. 6 A, Fig. 6 B and Fig. 6 C show the various scanning patters that generated by system shown in Fig. 5.
Fig. 7 shows five the orthogonal projection figure that ultrasonic image-forming system provided by Fig. 1.
Fig. 7 A shows by changing the orthogonal projection figure of the gauged Fig. 7 of deflection angle.
Fig. 8, Fig. 8 A, Fig. 8 B and Fig. 8 C show the transesophageal probe that is used for cardiac imaging and the importing and the use of the transesophageal probe of per nasal.
Fig. 9 A and Fig. 9 B are the sectional views of human heart that has the imaging probe that is inserted in the esophagus and be arranged in the ablation catheter of right ventricle.
Fig. 9 C is the projection of human heart.
Fig. 9 D is the projection that comprises the human heart of the top cutaway view that shows ablation catheter.
Figure 10 A, Figure 10 B and Figure 10 C are by the collected orthogonal projection figure of imaging probe shown in Fig. 9 A and Fig. 9 B.
Figure 11 A and Figure 11 B are the sectional views of human heart that has the imaging probe that is inserted in the esophagus and be arranged in the ablation catheter of left ventricle.
Figure 11 C is the projection of human heart that comprises the end cutaway view of the demonstration ablation catheter as shown in Figure 11 A and Figure 11 B.
Figure 11 D is the projection of human heart.
Figure 12 A, Figure 12 B and Figure 12 C are by the collected orthogonal projection figure of imaging probe shown in Figure 11 A and Figure 11 B.
Figure 13 A and Figure 13 B are the sectional views of human heart that has the imaging probe that is inserted in the esophagus and be arranged in the ablation catheter of left ventricle.
Figure 13 C is the projection of human heart.
Figure 13 D is the projection of human heart that comprises the top cutaway view of demonstration imaging probe as shown in Figure 13 A and Figure 13 B and ablation catheter.
Figure 14 A, Figure 14 B and Figure 14 C are by the collected orthogonal projection figure of imaging probe shown in Figure 13 A and Figure 13 B.
Referring to Fig. 1, transesophageal (TEE) imaging system 10 comprises transesophageal probe 12, and probe 12 has probe handle 14, and probe 12 links to each other with electronics compartment 20 with adapter 18 by cable 16, strain removing part 17.Electronics compartment 20 with keyboard 22 as the interface and be that video display units 24 is provided as image signal.Electronics compartment 20 comprises transmission beamformer, received beam maker and image composer.Transesophageal probe 12 has the distal portions 30 that links to each other with half elongated flexible body 36.The near-end of elongated portion 36 links to each other with the far-end of probe handle 14.The distal portions 30 of probe 12 comprises rigid region 32 and flexure region 34, and flexure region 34 links to each other with the far-end of elongate body 36.Probe handle 14 comprises that thereby being used to connect flexure region 34 makes rigid region 32 with respect to the register control 15 of the tissue orientation of being paid close attention to.Half elongated flexible body 36 can be inserted in the esophagus.Can utilize the far-end rigid region shown in commercially available gastroscope and Fig. 2 and Fig. 2 A to make transesophageal probe 12.The length of whole intubate is 110 centimetres, and diameter is 30F.Gastroscope for example is that (Skananteles Falls NY) makes by Welch Allyn.
Referring to Fig. 2 and Fig. 2 A, transesophageal imaging probe 12 is included in the far-end rigid region 32 that engaging zones 40 engages with flexure region 34.Remote area 32 comprises the distal tip shell 50 that is used to encapsulate ultrasound transducer array 42, electric connector and associated electronic components.Transducer array 42 is the two-dimensional array of a ultrasound transducer element preferably.Distal tip shell 50 comprises top shell 52 and upper top shell 54 down, and upper top shell 54 has ultrasonic window 56 and is positioned at the coupling medium of transducer array 42 fronts.The front portion of top shell 50 is the vertical bullet shaped (perhaps ball ball shape) with cavetto so that be inserted in the fornix and in esophagus and advance.In addition, housing 54 has the convex of surrounding window 56.Ultrasonic window 56 also can comprise ultrasonic lens and be used for cooling off and imbed the metal forming of lens material.
Transducer array 42 is bonded on the array backing 60, and each element of transducer links to each other with integrated circuit 62, as in U.S. Pat 5,267, described in 221.Integrated circuit 62 utilizes wire terminal 66 to link to each other with circuit board 64.This structure links to each other with radiator 68 in the mode of conducting heat.Transesophageal probe comprises two circuit 58 and 58A that flexural property is fabulous, and circuit 58 and 58A provide the connection between circuit board 64 and the probe connector 18.The fabulous circuit of flexural property has isotropic bending property, for example is folded into pleat shape or is wound in spiral type.Perhaps, can utilize coaxial cable to replace the fabulous circuit of flexural property.
Perhaps, imaging system 10 can be used the imaging probe of a kind of per nasal, esophagus.The imaging probe of per nasal, esophagus comprises the intubate that links to each other with the distal portions that has two-dimensional transducer array.The length of intubate is 100 centimetres to 110 centimetres, and diameter is 10F to 20F.Two-dimensional transducer array is bonded on the array backing, and each element of transducer links to each other with integrated circuit, describes in detail as top.
Fig. 3, Fig. 3 A and Fig. 3 B are the schematic sectional view of the flexure region 34 of transesophageal imaging probe 12.Imaging probe 12 comprises that the coupling mechanism that engages with register control 15 (Fig. 1) is to connect flexure region 34.Flexure region 34 has torsional rigidity and can not reverse basically.As described below, the clinician regulates register control 15 (Fig. 1) and connects flexure region 34 in every way, so that make rigidity remote area 32 location and make transducer array 42 with respect to the tissue volume orientation of being paid close attention to (as shown in Fig. 8 and Fig. 8 A).The clinician then can be with the locking position of coupled flexure region 34, with control at probe or the ultrasonic examination process in to keep the position of transducer array 42.In a preferred embodiment, flexure region 34 comprises a plurality of and at least one coupling link 71,72 or 80 that controllable push-and-pull cable (perhaps bar) is jointly arranged by making control handle 15 location.Coupling link is covered by flexible sheath 70.
Fig. 3 shows the flexure region 34 with the form connection of the J hook in the plane.Flexure region 34 is made by nearside chain 71, one group of chain 72 (as shown in Fig. 3 C) and the 75 distally chains 80 that link to each other with the far-end of high flexible push-pull bar 74 in the junction.The positioning control of control handle 15 is arranged in one or several pinion and racks of handle 14.When the mobile push-pull bar 74 in pinion and rack nearside ground, flexure region 34 is crooked and form the form of the J hook in the plane, and wherein rigid region 32 and flexure region 34 are positioned at same plane.The design form of the coupling link of jointly arranging with the push-pull bar 74 that links to each other with distally chain 80 at far-end 72 helps the bending in the plane.Coupling link 72 has been shown among Fig. 3 C.
Referring to Fig. 3 C, coupling link 72 has loop configuration, and loop configuration comprises the pivot-hinge fitting of the chain 72 that connects two vicinities.The pivot-hinge fitting comprises two the swivel pin 86A and the 86B (not shown in this perspective) that are arranged on the relative both sides of chain 72 and extend from recessed surperficial 88A and 88B (not shown) respectively.Hinged antelabium 90A and 90B comprise inner surface 91A (also not shown but describe for symmetry is described) and 91B, and inner surface 91A and 91B have the shape with the shape complementarity of surperficial 88A and 88B.Hinged antelabium 90A and 90B also comprise hole 92A and the 92B that is used to receive swivel pin respectively.
Coupling link 72 also comprises stop surface 94 and stop surface 96.Stop surface 94 is set at such position,, can be provided at the preselected maximum flexion of the attachment areas 34 that is promoted by each chain under the pulling function of push-pull bar 74 that is.Stop surface 96 is positioned at such height place, that is, the push-pull bar 74 in being arranged on raceway groove 73 can make attachment areas 34 adopt straight orientation when not spurring distally chain 80.Perhaps, design stop surface 96 is so that attachment areas 34 can adopt the orientation of any selection.For example, make attachment areas 34 can adopt opposite curvature in the time of can designing stop surface 96 with convenient push-pull bar 74 pulling distally chains 80.Coupling link 72 is made by plastics or metal, is positioned at pyrite or the rustless steel that inner electric wire provides electric screen such as also can be.The surface of coupling link 72 is designed to have the form of sheath, thereby also can make coupling link 72 crooked easily under the situation that does not have card or chuck 70.
Fig. 3 A shows the distal portions 30 with the form connection of out-of-plane J hook.Flexure region 34 is made by nearside chain 71, distally chain 80 and another group distally chain 82.Push-pull bar 74 extends to the coupling part 75 chain 80 from pinion and rack in raceway groove 73 (Fig. 3 C).Push-pull bar 76 extends to another pinion and rack (not shown) of close handle 14 from the far-end 77 that links to each other with distally chain 82.Move with crooked attachment areas 34 push-pull bar 74 nearsides.Push-pull bar 76 moves the distally chain 82 that links to each other with rigidity remote area 32; These two kinds are moved the form that forms the out-of-plane J hook with the out-of-plane flexure region 34 that moves to rigidity remote area 32.
Fig. 3 B shows the distal portions 30 with the form connection of the S hook in the plane.Flexure region 34 comprises nearside chain 71, chain group 72A, anchor chain 84, one group of chain 72 and the distally chain 82 that links to each other with rigidity remote area 32.Push-pull bar 74 extends near the pinion and rack that is positioned at the handle 14 from its far-end 75 that links to each other with chain 84.Push-pull bar 78 extends to and another pinion and rack that is arranged in modular catheter through chain 72, chain 84, chain 72A and chain 71 from its far-end 79 that links to each other with chain 82.Coupling link 72A is the mirror image of chain 72 basically, but comprises two raceway grooves that are used to receive push-pull bar 74 and 78.Chain 72 can connect on an orientation, and chain 72A can connect on the symmetric orientation of 180 degree.By the mobile push-pull bar 74 in nearside ground, pinion and rack starts proximal part the moving along a direction of attachment areas 34.In addition, by the mobile push-pull bar 78 in nearside ground, pinion and rack makes the distal portions of attachment areas 34 along another direction bending, thereby forms the S hook in the plane.That is, the S hitcher in the plane has flexure region 34 and the far-end rigid region 32 that is arranged in same plane.
Attachment areas shown in Fig. 3 B can be by further modification to comprise the push-pull bar 76 of the chain that is positioned at modification 72 as shown in chain 72A.By the mobile push-pull bar 76 in nearside ground, attachment areas 34 forms out-of-plane S hook.Out-of-plane S hitcher has the flexure region 34 that is arranged in a plane and bends to out-of-plane far-end rigid region 32.This layout can make transducer array 42 tilt and it is retracted with the required distance between the tissue that reaches and paid close attention to.The clinician controls control knob 15 and has been coupled to the position that transducer array 42 has required orientation with respect to the tissue volume of being paid close attention to until the top of probe.When transducer array 42 was suitably located, the clinician utilized brake that coupling mechanism is locked in its current position.After coupling mechanism was locked, imaging system was collected echo data, as shown in Fig. 8 and Fig. 8 A.
In a preferred embodiment, the TEE imaging system of TEE (through esophagus) imaging system or per nasal comprises transmission beamformer, received beam maker, image composer, surface detectors (perhaps edge detector) and image display, and the form with chart among Fig. 5 to Fig. 5 C shows all these parts.This system generates the front view of the novelty of several use planar imagings and projection imaging technology.The acquisition of image is at first described with reference to Fig. 4.Fig. 4 show transducer array 42 collected scan volume (that is the image volume) V of data.In the bearing range of the azimuth of selected elevation angle Φ, launch ultrasound lines by the transducer array 42 (described) that sends beamformer 200A collection with reference to Fig. 5 B.Transducer array 42 is gone up at selected sweep limits (R) and azimuth coverage (θ=± 45 °) and is detected by the periodic echo of received beam maker 200B to obtain the ultrasound data of a plane of delineation, as shown in Figure 4, and S0 for example.In order to make tissue volume V imaging, imaging system is at the S that is labeled as that is distributed on certain elevation coverage (Φ=± 30 °) -1, S -2, S -3, S 0, S 1, S 2And S 3Several planes of delineation (be called as 2D section or image sector) go up and collect data.
Fig. 4 A to Fig. 4 E shows by the example that has with reference to the different orientation of the collected scan volume of the imaging probe 12 of the described probe coupling part of Fig. 3 to Fig. 3 C.Particularly, Fig. 4 A shows by the collected image volume 100 of the imaging probe 12 of the flexure region 34 with straight extension.Imaging system is at above-mentioned several plane of delineation S -1, S -2, S -3, S 0, S 1, S 2And S 3On echo data.Fig. 4 B shows by the collected scan volume 120 of imaging system with flexure region 34 that connects with the J hook forms in the plane as shown in Figure 3.The J hook can be coupled on (as shown in Fig. 4 B) on the direction forward or direction backward, and as described with reference to Fig. 3 A, also can be moved to outside the plane.Fig. 4 C shows by the scan volume that imaging system generated 104 of tool with the flexure region 34 of out-of-plane J hook forms connection.Fig. 4 D and Fig. 4 E show when flexure region 34 connects with the S hook forms in the plane with out-of-plane S hook forms the scan volume 106 and 108 by imaging system was generated.
Fig. 5, Fig. 5 A and Fig. 5 B show the related imaging system of present preferred embodiment with the form of chart.As shown in Fig. 5 A, the whole operation of imaging system is by processor controls 140 controls.Processor controls 140 receives and comes from the instruction of importing controller 142 to 167 and provide signal for o controller 170 to 191.Processor controls 140 offers beamformer 200 with control data, and for image composer 250 provides the image control data, image composer 250 comprises to be handled and the demonstration electronic device.As in Fig. 5 B with shown in the form of chart, beamformer 200 comprises and sends beamformer 200A and received beam maker 200B.Usually, send beamformer 200A and received beam maker 200B for example as in U.S. Pat 4,140,022; US5,469,851; Perhaps US 5,345, simulation described in 426 or digital beamformer, and all these documents here are incorporated herein by reference.
According to an embodiment, transducer array 42 is the two-dimensional array of ultrasound transducer element preferably, can utilize electric-controlled switch that ultrasound transducer element is arranged to element group (that is subarray).Described switch selectively is joined together to form element of transducer the subarray with different geometric arrangement.That is, this two-dimensional array is an electrical arrangement.Switch also can make selected configuration link to each other with transmission beamformer 200A or received beam maker 200B as shown in Fig. 5 B.Each geometric arrangement of element of transducer is designed to make the ultrasonic beam of transmission or the received beam of detection to reach best form.
Can utilize the routine techniques described in the U.S. Pat 5,267,221 that licenses to people such as Miller on November 30th, 1993 to make transducer array 42.Element of transducer can have the interval of the Center-to-Center of 100-300 micron.Transducer supersonic frequency and required image resolution ratio are depended in the size of element of transducer and the interval between the element of transducer.
Referring to Fig. 5 B, this imaging system comprises transducer array 42, and transducer array 42 has specified transmission subarray 43 1, 43 2..., 43 MWith specified reception subarray 44 1, 44 2..., 44 NSend subarray 43 1, 43 2..., 43 MSend preprocessor 210 respectively with in the group 1, 210 2..., 210 MLink to each other, send preprocessor 210 in the group 1, 210 2..., 210 MAgain with transmission beamformer channel 215 1, 215 2..., 215 MLink to each other.Receive subarray 44 1, 44 2..., 44 NReceive preprocessor 220 respectively with in the group 1, 220 2..., 220 NLink to each other, receive preprocessor 220 in the group 1, 220 2..., 220 NAgain with received beam maker channel 225 1, 225 2..., 225 NLink to each other.Send preprocessor 210 in each group iComprise that one or more can provide the digital pulse generator that sends pulse can amplify with one or more and send pulse to encourage the voltage drive device of the element of transducer that links to each other.Perhaps, send preprocessor 210 in each group iComprise receiving and come from the conventional programmable delay line that sends the signal of beamformer.For example, the transmission output of commercially available ultrasonic system HPSonos 5500 can link to each other with transmission preprocessor 210i in the group, replace be at present that (they are all by Hewlett-Packard Company for the element of transducer of HPSonos 5500 manufacturings, now be Agilent Technologies, Inc., Andover, MA makes).
Receive preprocessor 220i in each group and can comprise addition delay line or the several programmable delay element that links to each other with adding element (summing junction).Receive preprocessor 220 in each group iPostpone each transducer signal; Increase the signal that postpones; And be a received beam maker channel 225 iThe signal of summation is provided.Perhaps, the interior receiving processor of group is several received beam maker channels 225 of a parallel received beam maker iThe signal of summation is provided.Parallel received beam maker can synthesize several received beams simultaneously.Receive preprocessor 220i in each group and also can comprise several addition delay line (programmable delay elements of perhaps many groups that are used for receiving simultaneously the signal that comes from several points, and each group delay element links to each other with summing junction), as the sequence number in proposition on May 28th, 1998 is No.09/085, describe in detail in 718 the U. S. application, sequence number is No.09/085, and 718 U. S. application here is incorporated herein by reference.
Processor controls 140 is transmission beamformer channel 215 through bus 2161 1, 215 2..., 215 MDelay instruction is provided and sends preprocessor 210 in organizing through bus 211 1, 210 2..., 210 MDelay instruction is provided.This delayed data is with the guiding of the transmission wave beam that generated and focus on the transmission scanning line of selected transmission figure, for example shown in Fig. 6 to Fig. 6 C.Processor controls 140 is a received beam maker channel 225 through bus 226 also 1, 225 2..., 225 NDelay instruction is provided and receives preprocessor 220 in organizing through bus 221 1, 220 2..., 220 NDelay instruction is provided.The guiding and the focusing of the received beam that the relative delay control that is applied is synthesized.Each received beam maker channel 225 iComprise variable gain amplifier, variable gain amplifier control is as the gain of the function of received signal depth, also comprises making acoustic data postpone with the guiding of sight line wave beam and synthesizing the delay element of the dynamic focusing of wave beam.Adding element 230 receives and comes from received beam maker channel 225 1, 225 2..., 225 NOutput and increase output and think that image composer 250 provides resulting beamformer signal, as in Fig. 5, being shown specifically.The beamformer signal indication is along a synthetic reception ultrasonic beam of received scanline.
According to another embodiment, transducer array 42 comprises the element of a greater number, and wherein only selecteed element links to each other with integrated circuit.Transducer array 42 has embarks on journey and each element of transducer that becomes row to arrange.Electric-controlled switch selectively is connected the adjacent element in the row and column.In addition, array also can comprise the electric-controlled switch that is used for selectively connecting element of transducer adjacent, that the diagonal angle is provided with.Selected element of transducer can link to each other with transmission or the receiving channels such as the imaging system of HP Sonos 5500 or the system that describes below.T/R (transmission/reception) switch optionally links to each other same set of pieces with transmission or receiving channels.Can directly connect or connect indirectly by one or more other element of transducer.
Utilization transmission beamformer suitably connects element in groups and makes the element phasing, can make the ultrasonic beam that is generated be sent out and be focused at required degree of depth place along required scanning line.The sequence number that various transducers connect as proposing on March 19th, 1998 is No.09/044, describes in 464 the U. S. application, and sequence number is No.09/044, and 464 U. S. application here is incorporated herein by reference.For example, can the element of transducer arow be linked together by the adjacent row switch of closure.Then each row is linked to each other with different system access channel, as shown in Fig. 5 B through the element of transducer of a selection of a selected row.Then, the element of transducer of phasing forms perpendicular to array plane and is the imaging plane of vertical (that is, being parallel to selected row).The absolute altitude direction is a level, as shown in Figure 4.
But imaging system can be utilized with respect to imaging plane (the S capable arbitrary orientation of transducer and that have row -1, S -2, S -3, S 0, S 1, S 2And S 3) generation scan volume V.For example, the interconnection of element of transducer in different row and columns and system access channel is to be provided as picture in the plane that is orientated at a certain angle with respect to the transducer row and column.For example, the element of transducer of adjacent row and column links to each other with beamformer with stepped figure.This layout provides and the parallel plane image that is orientated with 45 degree with respect to the row orientation.In another embodiment, element of transducer links to each other with beamformer and is about circular contour line with formation.This has improved the absolute altitude focus control.The acoustic centre of source can be placed on any element that links to each other with system access channel.Usually, wait the delayed profile line and this transducer arrangement is combined with the absolute altitude focus control by what determine to be fit to along these contour line Connection Elements.
Imaging system is obtained echo data by carrying out selected scanning patter on the selected size of volume V.Fig. 6 shows for example by being collected in several planes of delineation (2D section) S described with reference to Figure 4 -1, S -2, S -3, S 0, S 1, S 2And S 3On the 100% rectangular scanning figure 240 carried out of echo data.But in order to reduce sweep time, imaging system can be carried out data scanning on the smaller volume that with the tissue regions of being paid close attention to is the center.For example, Fig. 6 A shows oval scanning patter 242, and it comprises 70% of scanning line used in as shown in Figure 6 the rectangular scanning figure 240.Fig. 6 B shows lozenge diagram 244 1, it has only comprised 50% of scanning line, and Fig. 6 C shows star graphic 246, it has only comprised 25% of scanning line.
Referring to Fig. 7, imaging system can generate and show several at two that have zero degree azimuth and absolute altitude position respectively orthogonal central plane S 0And L 0(Fig. 4) figure of Nei uniqueness.The figure that is generated is included in the projected image that generates on the whole zone of the zone paid close attention to or 2D section.Particularly, make planar S when direction from y=∞ towards y=0 0During (elevation angle Φ=0 °) imaging, this figure is called as front projection Figure 28 6.Back projection (not shown among Fig. 7) is that direction from y=-∞ towards y=0 is by imaging.Be in the direction from x=∞ towards x=0 and the L of direction imaging from x=-∞ towards x=0 0The image sector of (azimuth angle theta=0 °) is called as right side projection 292 and left side projection 291 respectively.Imaging system can generate and show top projection 337, and this top projection 337 is modification C-scan images of the selected tissue surface of the direction imaging from z=∞ towards z=0.The position of modification C-scan image can be by preliminary election, be limited in the plane graph (plane of delineation) or be limited among front projection figure or the figure of lateral projection, as shown in Figure 7.Imaging system also generates and shows that end projection 336, end projection 336 are modification C-scan images of the selected tissue surface of the direction imaging towards z=∞ from z=0.But projecting direction usually needn't be parallel with x, y or z axle, but any direction of selecting by the clinician.
Imaging system is designed to be able to provide the figure of being convenient to clinician's understanding.As shown in Figure 7, image display is positioned at the center with front projection figure (286), and left side projection (291) is positioned at left-hand side, and the right-hand side that right side projection (292) is positioned at front projection figure.In addition, image display is presented at the top of front projection figure with top projection (337), and end projection (336) is presented at the below of front projection figure.Back at each figure has display icon.Display icon 370,372,374,376 and 378 provides orientation and provides relevant Figure 28 6,291,292,337 respectively and 336 sweep limits.The clinician can be based on the Information Selection and preliminary election sweep parameter and the parameters of display that are provided in each figure and the display icon.This system then generates new figure and relevant display icon, describes as following.
Fig. 7 A shows the new orthogonal graph of the Fig. 7 that recomputates for 30 deflection angles of spending.Left side projection 291A and right side projection 292A correspond respectively to left side projection 291 and right side projection 292 (Fig. 7).Left side icon 372A and right side icon 274A show the new viewing area after recomputating deflection angle.Similarly, top icon 376A and base map mark 378A shows deflection angle for the clinician.
Importantly, imaging system can generate projected image on the whole zone of plane graph or on the zone of being paid close attention to of plane graph (that is 2D sectioning image) the back qualification that is being obtained by clinician observation post.If only on the zone of being paid close attention to, generate projected image, so each image be included in the zone of being paid close attention to projection and at the plane graph (2D section) of the region exterior of being paid close attention to.Particularly, right side view be included in paid close attention to the zone in the right side projection and at plane L 0The plane graph at place.Similarly, left side view be included in paid close attention to the zone in the left side projection and at plane L 0The plane graph at place.That is, Figure 29 1 and 292 (perhaps 291A and 292A) is only different in the zone of being paid close attention to, left side projection and right side projection be generated and situation about showing under, and paid close attention to regional outside be identical.
Imaging system is initially the clinician front view and side view is provided.Imaging system also is provided at the C-scan image of at least one modification on the scan volume, the C-scan image of this modification is perpendicular to the image on front view plane and the planar selected surface of side view, and V.A clinician can manually select (perhaps this system can select automatically) to be displayed on surface in the C-scan image of modification.Imaging system generates these rectangular projection figure with the frame frequency that (is preferably in more than the 20Hz, perhaps in the scope of 30Hz to 100Hz) more than the 15Hz in real time.
Referring to Fig. 5, Fig. 5 A and Fig. 5 B, imaging system comprises image composer 250 and the image display that sends beamformer 200A and received beam maker 200B, processor controls 140, comprises surface detectors or edge detector.As shown in Fig. 5 A, processor controls 140 provides control data for beamformer 200, such as time limit 170, scanning wire size 171 and scope 175, thereby is controlled at the interior scanning of graphical sector.In another embodiment, send beamformer 200A the transmission that comes from element of transducer is carried out phasing to send ultrasonic beam along the transmission scanning line at several intervals selected on angular distribution in pie-shaped section.In receiving mode, received beam maker 200B carries out phasing to detect ultrasonic echo along one or several received scanlines at interval selected on angular distribution to element of transducer.For example in U.S. Pat 4,140,022; US 4,893, and 283; US 5,121, and 361; Perhaps US 5,469, described the transmission beamformer that links to each other with phased array and the operation of received beam maker in 851.
In order to limit the parameter of B-scan, processor controls 140 receives the input data that limit the sector scanning degree of depth 148, frame frequency 150 and orientation/absolute altitude scanning ratio 152.The sector scanning degree of depth limits the sweep limits (R) of detected echo, and for example 4 centimetres, 8 centimetres or 10 centimetres, this depends on the position of transducer array with respect to the physiological tissue that is paid close attention to.The clinician can select frame frequency 150 according to the organizational structure of being paid close attention to.For the real time imaging of movable organ, frame frequency is necessary for several at least frames of per second to avoid owing to moving of tissue makes image blurring.User also selects orientation/absolute altitude scanning than 152, the scanning of orientation/absolute altitude makes B-scan from the big azimuth scan of single sector (promptly than 152, the polarizers of big angle scope of the scanning line in image sector) variation in the scope of the minimum azimuth scan of carrying out to a large amount of sectors (that is the small angle range of each sector of in big absolute altitude displacement, scanning).Like this, orientation/absolute altitude scanning provides the bottom view image aspect ratio (that is, the x/y size) of bottom view 336 and the top view image aspect ratio of top view 337 than 152 for C-scan, as shown in Figure 7.
Processor controls 140 is according to the angular spacing between the scanning line of the preferred sector scanning degree of depth, frame frequency, orientation/each sector of absolute altitude scanning ratio calculating and the number of scanning line (171).Based on initial value, processor 140 distributes the scanning wire size of maximum possible and the sector of maximum possible.Particularly, processor 140 calculates the angular spacing between the scanning sector, that is, and and the number of sector angle (173) and sector (174).Processor controls 140 provides these numerical value for beamformer 200.
The scanning sequency that processor controls 140 is selected by beamformer 200 execution.Send beamformer transmission along scanning line guiding phasing ultrasonic beam in the scope that each sector is calculated.For the scanning line of each transmission, the received beam maker carries out phasing to detect ultrasonic echo along corresponding received scanline to element of transducer.Perhaps, the received beam maker is synthetic come from selected angular distribution at interval the scan-data of several received scanlines, for example the sequence number that proposes on March 24th, 1998 is No.09/046,437, describe in the U. S. application of title for " improving the frame frequency of phased array imaging system ", sequence number is No.09/046, and 437 U. S. application here is incorporated herein by reference.Utilization has frequency and for the wave filter up to the passband below 60% of the mid frequency of 10MHz the RF data is carried out filtering, and the frequency of described passband is preferably 35% of mid frequency in the scope of 5MHz to 7MHz.
Processor controls 140 time of reception gain compensations (TGC) input 142, lateral gain compensation (LGC) input 144 and the absolute altitude gain compensation (EGC) that is provided by the clinician or be stored in the memorizer import 146.The receiving channels gain of the function of the distance between conduct and the transducer array is regulated in TGC (time gain compensation) control usually in discontinuous step.TGC control has compensated the decay of ultrasound wave by broadcasting media the time.LGC (lateral gain compensation) control break as the receiving channels gain of the function of the azimuthal displacement of particular scan, but along the gain of scanning line be not subjected to and transducer array between the influence of distance.Make under the situation that ultrasonic signal reduces in the specific region in the anatomical structure owing to this tissue, perhaps the tissue orientating in the patient causes echo-signal to have under the situation of intensity of variation, and LGC control needs.EGC (absolute altitude gain compensation) control break promptly, is regulated the gain of a selected scanning sector (that is scintigram) as the receiving channels gain of the function of absolute altitude displacement.User also can manual mode readjusts TGC, LGC and EGC so that image " seems " better.
Referring to Fig. 5, received beam maker 200B provides the RF echo-signal of detection for image composer, image composer comprises time gain compensation device (TGC) 262, lateral gain compensation device (LGC) 264 and absolute altitude gain compensator (EGC) 266, and image composer carries out above-mentioned correction.EGC266 is B-scan signal processor 272, C-scan signal processor 315 and edge detector 302 and 322 signal that affords redress.
Perhaps, utilize reasonable gain compensation (RGC) to replace TGC262, LGC264 and EGC266, in U.S. Pat 5,195,521 and at " Rational Gain Compensation forAttenuation in Cardiac Ultrasonography; " Ultrasonic Imaging, the 5th volume is described reasonable gain compensation (RGC) in the 214-228 page or leaf (nineteen eighty-three).RGC is compensate for attenuation when distinguishing blood and heart tissue.RGC utilizes a threshold value, and back-scattered signal is restricted to " zero " when being lower than this threshold value, changes the signal gain of blood and heart tissue.In this case, back-scattered signal comes from blood.
Referring to Fig. 5, image composer comprises can receive the filtering that comes from envelope detector 274 and 317 and the preprocessor 276 and 318 of offset data.Preprocessor 276 and 318 is by being plotted to data the contrast of each data point of control on the one group selection curve.After the contrast level is distributed to each data point, can use the scan line buffer device to preserve the data of scanning line temporarily.
Image composer comprises scan-line data body memory 278 and data boundary body memory 280.Scan-line data body memory 278 receives the echo data handled and from processor 140 reception demonstration wire size 172, sector number 174 and scopes 175.Data volume memorizer 278 is by distributing to each sector one number and another number be distributed to each scanning line on azimuth direction.The size that is stored in the data matrix in the data volume memorizer 278 depends on frame frequency.Each scan period (that is sound frame) is utilized the data filling data matrix that is obtained on the scan volume of being described by bearing range and absolute altitude scope.The scanning wire size is corresponding to row in the data volume matrix number.Sector number is corresponding to the row in the data volume matrix number.The sweep limits data are corresponding to the row height in this data volume matrix.Data volume memorizer 278 provides its output 279 to observe processor 285 and 290.
The data that data boundary body memory 280 also receives processed echo data and comes from majority vote processor 308.Data boundary body memory 280 also receives demonstration wire size 173, sector number 174, scope 175 and the B-scan surface contrast 179 that comes from processor 140.Data volume memorizer 280 is also stored data with the form of matrix.Data volume memorizer 280 provides its output 281 to observe processor 285 and 290.
Orientation diagram interpolation processing device 285 and absolute altitude figure interpolation processing device 290 receive data that come from memorizer 278 and memorizer 280 and the data that come from B-scan edge indicator 310 and C-scan edge indicator 330.According to the figure input, interpolation processing device 285 and 290 generates selected front view and selected side view respectively.Front view and side view are provided for display plane memorizer 300, and display plane memorizer 300 offers video display units with video signal 350 again.According to the B-scan data, the clinician can select to comprise the zone of selected tissue regions.The clinician limits the zone of being paid close attention to (ROI) and selects the tissue paid close attention to by the setpoint distance storbing gate or around the imaging tissue.
Imaging system be designed to automatically work or with the interactional form of clinician.The clinician can draw the profile in the zone of being paid close attention to by seeing front plan views or side plan view (that is B-scan image).Based on the profile of being drawn (perhaps other input), processor controls 140 converts R0I (zone of being paid close attention to) girth input 153 to scope 175, and ROI indicates and gate 176.They can be displayed on the video display units to show the profile in a zone.They also can be provided for edge detector 302 and edge detector 322 detects to carry out surface (border) in response to the echo that comes from the point in the ROI.Like this, can make surface detectors (that is, at least one edge detector 302 or 322) in the ROI girth, set up the projecting figure zone, manifest thereby make surface detectors carry out the surface.
Notice that tissue surface or organizational structure are usually in single plane graph or figure scope and to fluctuate outward be important.The related ultrasonic system of several prior aries can only show echo data with 2D section or planar form.Such plane graph can provide the zone that has at random to piece together.It is considered herein that the clinician manifests or understands such plane picture may be difficult, particularly when transducer array not with the surface of being paid close attention to fully on time.In order to address this problem, imaging system of the present invention is utilized planar imaging and projection imaging to come the visualize tissue surface and is manifested the intravital 3 D anatomy structure of patient (comprising therapy equipment, the diagnostic equipment, apparatus for correcting, intravascular stent etc.) usually.
As shown in Fig. 5 B, B-scan edge detector 302 comprises signal processor 304, organizes indicator 306, majority vote processor 308 and edge indicator 310.U.S. Pat 5,195,521 (document here is incorporated herein by reference) have disclosed a kind of majority vote (majority vote) circuit and have been used to generate the circuit in ROI (zone of being paid close attention to).Processor controls 140 is enabled output 176, wire size output 171 and sector number output 174 for edge detector 302 provides ROI.Signal processor 304 obtains feature to the difference sensitivity between the echo that comes from tissue and the echo that comes from blood to improve organizational boundary's locating accuracy according to the RF data.This feature is the whole backscattered amplitude that comes from tissue and come from blood.Signal processor 304 is determined whole backscattered amplitude and provides it to organize indicator 306.(perhaps, organize indicator 306 can directly receive echo RF data.)
Organize indicator 306 to come from the signal of the judgement output 1 or 0 of tissue or blood according to echo.Majority vote processor 308 determines that most of signals of each scanning line in the scanning sector are 0 or 1.That is, majority vote processor 308 produces one about coming from the echo of tissue by the signal indication of organizing indicator 306 to be provided or coming from the signal indication of the echo of blood at each scope place.Majority vote processor 308 produces this signal for the most of continuous sweep lines that comprise the current line that is scanning.If indicator 306 is illustrated in the signal that a reflection in the scope comes from tissue for most of line outputs, the 308 output expression reflections of majority vote processor come from the signal of organizing such situation so.Similarly, if indicator 306 is exported different signals for most of lines, another expression reflection of majority vote processor 308 outputs comes from the signal of the such situation of blood so.
The short pulse that is used to form the contour line of chamber in this image or chamber with generation is provided along with the variation of the signal that is provided by majority vote processor 308 edge indicator 310.Particularly, edge indicator 310 comprises that the edge indicator circuit is (in U.S. Pat 5,195, described in 521), no matter when the output of majority vote processor 308 becomes low level from high level, the edge indicator circuit is for example exported high logic level in the time of 1 microsecond, vice versa.The output 312 that comes from edge indicator 310 is provided for processor 285 and 290 so that B-scan border highlight.In addition, the output 309 that comes from majority vote processor 308 is provided for above-mentioned data boundary body memory 280.
C-scan edge detector 322 is to work with B-scan edge detector 302 similar modes.C-scan edge detector 322 comprises signal processor 324, organizes indicator 326, majority vote processor 328 and edge indicator 330.Processor controls 140 is enabled output 177, wire size output 171 and sector number output 174 for edge detector 322 provides range gating.Signal processor 324 obtains to come from tissue and come from the whole backscattered amplitude of blood and provide it to organize indicator 326 according to the RF data.Organize indicator 326 to come from the signal of the judgement output 1 or 0 of tissue or blood according to echo.Majority vote processor 328 determines that most of signals of each scanning line in the scanning sector are 0 or 1.That is, majority vote processor 328 produces one about coming from the echo of tissue by the signal indication of organizing indicator 326 to be provided or coming from the signal indication of the echo of blood at each scope place.
As described for edge indicator 310, the short pulse that is used to form the contour line of chamber in this image or chamber with generation is provided along with the variation of the signal that is provided by majority vote processor 328 edge indicator 330.Particularly, no matter when the output of majority vote processor 328 becomes low level from high level; That is, detection of echoes changes to blood from tissue, edge indicator 330 output high logic levels, and vice versa.The output 332 that comes from edge indicator 330 is provided for processor 285 and 290 so that C-scan border highlight.In addition, the output 329 that comes from majority vote processor 328 is provided for gating peak detector 320.
Referring to Fig. 5 C, gating peak detector 320 provides the C-scan of following the selected tissue surface that is positioned at selected ROI or scope data.Sampler 352 receptions come from the output 319 of preprocessor 318 and the data of sampling are offered holding circuit 356 and delay circuit 360.In addition, the output 329 of majority vote processor 328 is provided for positive trigger comparator 354 and negative trigger comparator 358.When majority vote processor 328 detected near tissue surface, positive trigger comparator 354 was enabled signal for holding circuit 356 provides, and holding circuit 356 offers its output 357 near/surface circuit 364 far away again.
The clinician utilizes input 162 to select top view or bottom views, and processor controls 140 nearly/surface far away output 184 offers near/surface circuit 364 far away, near/surface circuit 364 far away is as a switch.When majority vote processor 328 was detecting surface far away, negative trigger comparator 358 was enabled signal for holding circuit 362 provides, and holding circuit 362 offers its output 363 near/surface circuit 364 far away again.Closely/far surface circuit 364 receives the near/face value 184 far away that comes from processor controls 140.According to closely/surface far away output 184, near/switch far away regulates processor 335 for deflection angle and contrast adjustment processor 340 provides signal 357 or 363.That is, near/switch 364 far away determines that 320 transmissions of gating peak detector come from the just extrorse big numerical value of RF signal or the big numerical value at the negative sense edge that transmission comes from the RF signal.Like this, system has generated the data of top view and bottom view (all being the C-scan image of modification).
As mentioned above, gating peak detector 320 is selected surface data near or far away and sends it to deflection angle to regulate processor 335 from the RF signal.Regulate (that is, deflection angle is regulated output 183 and equalled zero) for zero degree, these data are provided for contrast adjustment processor 340 without change so.Contrast adjustment processor 340 carries out independent contrast adjustment for bottom view and top view (that is two C-scan images).The clinician provides C-scan contrast input 156, and processor controls 140 provides C-scan output 178 according to C-scan contrast input 156.For example, the form that tissue can white line goes up in sight at front view and side view (B-scan cross section), but the clinician may want to observe to seek boundary mark, damage or therapy equipment in bottom view with gray form.The C-scan contrast has produced real tissue surface situation.After contrast adjustment, contrast adjustment processor 340 is regulated processor 345 for convergent-divergent the contrast adjustment data is provided.Convergent-divergent is regulated processor 345 and is drawn the contrast adjustment data to be used for front view and side view (that is B-scan image) and to go up and to provide data for video display units memorizer 300 with certain proportion.
Ultrasonic image-forming system 10 provides six-freedom degree to obtain and to regulate image.Electrical adjustment provides three degree of freedom to obtain selected figure orientation.Three degree of freedom comes from the spatial orientation of transducer array 42 with respect to selected organizational structure in addition.Make transducer array 42 orientations by connecting the attachment areas 34 shown in Fig. 3 to Fig. 3 B.Connect the orientation that changes scan volume, thereby as shown in Fig. 4 A to Fig. 4 E, change the orientation of front view, side view and bottom view.Image composer 250 provides educible and engineering three-dimensional tissue structures figure that be convenient to understand.
Can in the mode of electronics rectangular projection Figure 28 6,291 and 292 be reorientated by new input value is provided for processor controls 140.After observing front view 286 (perhaps rearview) and side view 291 or 292, the clinician can be by input about scanning sector deep 148, frame frequency 150 or orientation and absolute altitude scanning changes than 152 modes with electronics or scan volume V is reorientated, thereby carries out another scanning.Perhaps, the clinician can reselect the imaging tissue by the spacing compensation 158 or the roll compensation 159 that change new scanning.The spacing compensation changes scanning line on azimuth direction.Roll compensation changes the absolute altitude of line with respect to transducer array 42, thereby as shown in Figure 4, changes the position of each image sector.Like this, the clinician can be on the less data volume at the center that is organized as paid close attention to boot scan.By in the enterprising line scanning of smaller volume, this system can be by improving the realtime imaging that frame frequency improve movable organ, and this is because it has collected less data point.Perhaps, the data point of equal number is collected to improve resolution by this system on less volume.
Imaging system 10 uses several icons that intelligible image is provided.Referring to Fig. 5, Fig. 5 A and Fig. 7, orientation icon maker 289 receives spacing adjusting 181 and provides data to show preceding orientation diagram mark 370 (the perhaps back side icons of rearview) of front view.Absolute altitude icon maker 299 receives and rolls adjusting 182 and the left absolute altitude icon 372 (Fig. 7 shown in) of data to show left Figure 29 1 and the right absolute altitude icon 374 of right Figure 29 2 are provided.Deflection angle icon maker 346 receives deflection angle adjusting 183 and data top icon 376 and base map mark 378 (Fig. 7) to show expression deflection angle orientation is provided.The clinician uses icon can understand image better.In addition, clinician's selective value of using icon that acoustic beam is controlled and is directed to be paid close attention to or make framing and orientation with respect to the orientation of transducer array 42.
Imaging system 10 also can electronics mode change the expression of orthogonal projection figure (that is, forward and backward, side, top and bottom view).After observing front view and side view (as shown in Figure 7), the clinician can be by changing the orientation that deflection angle compensation 160 changes figure.Deflection angle output 183 is provided for processor 285,290 and 335, before 285,290 and 335 pairs of the processors, side, top and bottom view recomputate.The front view 286A that recomputates, left side view 291A, right side view 292A, top view 337A and bottom view 336A are as shown in Figure 7A.In addition, orientation icon maker 289 provides data to show front view orientation side view 370A, and absolute altitude icon maker 299 provides data to show left figure absolute altitude icon 372A and right figure absolute altitude icon 374A.Deflection angle icon maker 346 provides data to show top view icon 376A and bottom view icon 378A.
Deflection angle is regulated needs interpolation to generate new scanning line plane usually.These be utilize the data volume matrix by nearest one group of scanning line produce to produce new datum plane (that is sector).This interpolation method use with by polar data being converted to the identical principle of scan conversion method that the used real-time 2D system that carries out coordinate data of display carries out (for example, see U.S. Pat 4,468,747 or US 5,197,037).Each datum plane that recomputates can be stored in the memorizer relevant with processor 285 and 290.This datum plane that recomputates is provided for video display units flat memory 300, then utilizes signal 350 to provide it to video-frequency monitor (as shown in Figure 5).The ultrasound data about R, θ that scan converter 288 and 298 will obtain converts the XY form that is used for orientation and indexed plane to.Scan converter 288 and 298 formation are as in U.S. Pat 4,468,747; US 4,471, and 449 or US 5,197,037; Perhaps " Ultrasound Imaging:an Overview " and " A Scan Conversion Algorithmfor Displaying Ultrasound Images ", the Hewlett-PackardJournal in October nineteen eighty-three, described in.
Importantly, whole system provides six-freedom degree to obtain and to produce high quality graphic.Imaging probe 12 three degree of freedom is provided so that transducer array 42 with respect to checked tissue positioned.By connection, rotation and mobile distal portions 30, the clinician controls transducer array 42 selected position and makes array 42 with respect to checked tissue positioned.The image-forming electron device provides other three degree of freedom to produce image by selecting spacing, rolling and deflection angle numerical value.Display system can produce new (redirecting) image that is used for different deflection angle numerical value according to the collected scan-data that is stored in the memorizer.Display format always is educible and is convenient to clinician's connection to another from a position (perhaps position range), describes as following.The clinician will be owing to the TEE of TEE (through esophagus) or per nasal probe and is provided the probe designs of novelty of the display system of the novelty that the anatomical structure of image proofreaies and correct orientation to understand three dimensional structure (in real time).This novel probe designs has the centrage of the transducer array 42 at the place, summit that is positioned at the cake chart picture as shown in Fig. 9 A to Figure 14 C.
Referring to Fig. 8, before collecting data, the transesophageal probe that the clinician has guiding introducer 135 enters into esophagus 380 by mouth 130, throat 132.After probe and the outstanding heap soil or fertilizer over and around the roots vertical 133 of introducer process, the distal portions 50 of probe is positioned at the position that needs of GI track.The distal portions 50 that has transducer array 42 can be positioned at esophagus, as shown in Fig. 8 B, perhaps is positioned at the bottom of stomach, as shown in Fig. 8 C.For to cardiac imaging, sending beamformer makes the pulse concentration of emission at bigger degree of depth place, and the received beam maker detects the echo come from apart from 10-20 centimetre of structure far away, compares with scope used in the catheter in blood vessel in being inserted into heart for example, and its scope is far a lot.
Perhaps, as shown in Fig. 8 A, the transesophageal probe of per nasal that the clinician will have nose introducer 136 is directed in the left nostril 134 (perhaps right nostril), and they are moved in nasopharynx, enters into esophagus 380 through outstanding heap soil or fertilizer over and around the roots vertical 133.Nose introducer 136 has bigger internal diameter and has thin softish wall.In the importing program, the TEE of per nasal probe can support the sheath of nose introducer 136.Two elements all are crooked to conform to the internal geometry of patient's ductus nasopharyngeus.After importing, the TBE of per nasal probe moves down in esophagus 380 and the far-end that has a transducer array is positioned at the position that needs of GI track.
Similar with the TEE imaging probe, the TEE of per nasal probe is positioned at esophagus (as shown in Fig. 8 B) or is positioned at bottom (as shown in Fig. 8 C) and its orientation of stomach 381 can be to the imaging of tissue of being paid close attention to.Under each situation, imaging system produces the image of several novel type.Imaging system is specially adapted to utilize near examination scope near imaging of tissue, and this is because it can provide realtime imaging about movable organ such as heart.
Referring to Fig. 8 B and Fig. 8 C, imaging probe can be to the medical treatment device imaging, such as the balloon catheter or the ablation catheter that are inserted in the heart.Ablation catheter 400 (for example, by Medtronics, Inc., the conduit that Sunnyvale, CA make) is inserted in the left ventricle 394, and its distal portions 402 is positioned near the inner surface of cardiac muscle 399 or on it.The clinician will understand three dimensional structure (in real time), and this is owing to above-mentioned probe novel designs causes.Novel display system provides the anatomical structure of the orthogonal projection figure described in operated key Fig. 7 and Fig. 7 A to proofread and correct orientation.
Fig. 9 A is the cross-sectional view of human heart along its long axis, and Fig. 9 B is the cross-sectional view along the minor axis of heart.Fig. 9 A to Fig. 9 D is not displayed on the video display units of imaging system, is for convenience of explanation but provide here.Fig. 9 A and Fig. 9 B show the distal portions 30 (as shown in Fig. 1 and Fig. 2) of the probe 12 that is arranged in esophagus 380 (Fig. 8 B) and the distal portions 402 that also is positioned at the ablation catheter 400 of right ventricle 386.
Imaging system uses transducer array 42 to collect echo data and its orthogonal projection figure is provided (that is, having the figure of the orientation of perpendicular each other), as shown in Figure 10 A, Figure 10 B and Figure 10 C.These three orthogonal projection figure are front view 420, left side view 450 and top view 470, and they are to have in the zone of being paid close attention to or the plane graph of the projection in the scope of being paid close attention to.The video display units of imaging system shows each orthogonal projection figure and relevant icon, described in reference Fig. 7 and Fig. 7 A.In the following description, we utilize the standard definition of projection, for example at Engineering Drawing and Geometry, are shown John Wiley ﹠amp by R.P.Holster; Sons, Inc. provided in 1961.
Referring to Fig. 9 A, with the transducer array 42 of phased array pattern operation by line 412 and 413 and the azimuth coverage drawn of range distance 414 on collect echo data.Figure 10 A shows corresponding front view 420 and front view icon 430.Front view icon 430 comprises array axis 432 and shows preceding visual field 434 corresponding to azimuth coverage.Array axis 432 shows the longitudinal axis for the transducer array 42 of the selected numerical value (Fig. 7 A) of deflection angle adjusting 243.In Figure 10 A, front view 420 shows the distal portions 402 that is positioned at the ablation catheter 400 on the nearly surface (top surface) 389 of right ventricle 386 and left ventricle 394 isolating barrier films 388 (as shown in Fig. 9 A).Front view 420 also partly shows the aortic valve 395 between left ventricle 394 and aorta 396.The clinician can set gate 416 and 417 and ROI indicate 415 position.
Referring to Fig. 9 B and Figure 10 B, imaging system also can by by line 445 and 446 and ROI indicate and to collect echo data on the 448 selected elevation coverages of drawing and produce left side view 450.Transducer array 42 (Fig. 9 A) is collected echo data on the image sector of selecting quantity, its planar position of center line 470 expression front views.Left side view 450 has shown a part, right ventricle 386, the barrier film 388 of left ventricle 394 and has been positioned at the distal portions 402 of the conduit 400 on the right ventricle surface 389 of barrier film 388.Referring to Figure 10 B, left figure icon 460 shows available side-looking field 462 and elevation coverage 464, obtains image sector in side-looking field 462 and elevation coverage 464.
Fig. 9 C and Fig. 9 D are the projections of human heart.Fig. 9 D show show as the scope (that is gate 416 and 417) defined in Fig. 9 A and Fig. 9 B in the top-sectional view on surface 389 of the distal portions 402 of excision conduit and barrier film 388.Corresponding Figure 10 C has shown the C-scan projection top view 470 that is produced by the B-scan data in range gating door 416 and 417, and has shown top view icon 490.Top view 470 show be positioned at barrier film 388 near surperficial 389 on the distal portions 402 of conduit 400. Range gating door 416 and 417 and angle range line 412,413,445 and 446 define the area of top view 470.The area of top view 470 is not equal to shaded area, and this is because near surperficial 389 curvature of barrier film 388 causes.Figure 10 C has also shown top view icon 490, and top view icon 490 comprises rectangular array 492 and array axis 494.Axis 494 is represented the deflection angle of top view 470 with respect to the angle on the limit of rectangular area 492, and wherein in this case, deflection angle equals zero.
Figure 11 A and Figure 11 B show the cross-sectional view with heart like Fig. 9 A and Fig. 9 category-B.Imaging system has shown corresponding front view 420A (as shown in Figure 12 A) and left side view 450A (as shown in Figure 12B).But, in the image shown in Figure 12 A and Figure 12 B, imaging system is used and the different range gating door 416 shown in Figure 10 A and Figure 10 B and 417 and the numerical value of angle range line 412,413,445 and 446, and this is that distal portions owing to conduit 400 is positioned at left ventricle 394 at present.In addition, imaging system has shown bottom view 500 (as shown in Figure 12 C), rather than top view 470 (as shown in Figure 10 C), behind the range gating door 416A and 417A that set as shown in Figure 12 A and Figure 12 B.
Figure 11 A is the cross-sectional view of heart along the major axis cross section.Imaging system is collected echo data and is produced preceding orthogonal projection Figure 42 0A, as shown in Figure 12 A.This system uses a new azimuth coverage of being drawn by line 412A and 413A, and it is less than the used azimuth coverage of projection 420.Select less azimuth coverage to be because the surface distance array of being paid close attention to 42 is far away.Usually, in the phased array pattern, compare with zone far away, azimuth that the imaging system utilization is bigger and elevation coverage are to the regional imaging of being paid close attention near array 42.
Referring to Figure 12 A, front view 420A has shown the part of distal portions 402, left ventricle 394, Bicuspid valve 392 and the aortic valve 395 of barrier film 388, conduit 400, and all these is in scope 414A.Front view 420A can show the distal portions 402 of conduit 400, for example in the process of the excision of cardiac muscular tissue or revascularization.Figure 12 A has also shown front view icon 430A, front view icon 430A comprise with corresponding to the angled array axis 432A of actual preceding visual field 434A of the azimuth coverage that limits by line 412A and 413A.Front view icon 430A comprises corresponding to the preceding visual field 436A of the usefulness of maximum azimuth coverage.Figure 11 B is the cross-sectional view of heart along minor axis.Figure 11 B shows the distal portions 30 (being positioned at esophagus 380) of probe 12 and is positioned at the distal portions 402 of the ablation catheter 400 of left ventricle 394.
Figure 12 B has shown left side view 450A and left side view icon 460A.Imaging system produces left side view 450A, left side view 450A show the left ventricle 394 that is filled with oxygen containing blood a part, be filled with the part of right ventricle 386 of the blood of deoxidation.The distal portions 402 of conduit 400 is positioned in range gating door 416A and 417A near the far away surperficial 389A (basal surface) of barrier film 388.Left side view icon 460A shows available side-looking field 462A and actual side-looking field 464A.Actual side-looking field 464A shows the elevation coverage of the line that is sent by transducer array 42, and it is drawn by line 445A and 446A.Available side-looking field 462A is corresponding to the maximum elevation scope.
Figure 11 C and Figure 11 D are the projections of human heart.Figure 11 C shows the bottom sectional view that shows as the basal surface 389A of distal portions 402 in the scope defined in Figure 12 A and Figure 12 B and barrier film 388.Figure 12 C has shown the C-scan projection bottom view 500 that is produced by the B-scan data in range gating door 416A and 417A.Bottom view 500 shows the distal portions 402 on the far away surperficial 389A (left ventricle surface) that is positioned at barrier film 388. Range gating door 416A and 417A and angle range line 412A, 413A, 445A and 446A define the area of the bottom view 500 shown in Figure 12 C.The area of bottom view 500 is not equal to shaded area, and this is because the curvature of nearly surperficial 389A causes.Figure 12 C has also shown bottom view icon 520, and bottom view icon 520 comprises rectangular array 522 and array axis 524.Axis 524 is represented the deflection angle of bottom view 500 with respect to the angle on the limit of rectangular area 522, and wherein in this case, deflection angle equals zero.
The video display units of imaging system shown above-mentioned orthogonal projection figure and always has been in the relevant icon of same position, as shown in Figure 7.The facility of each image and icon location is proofreaied and correct the image of the easier actual anatomical structures for the imaging tissue of clinician.After another deflection angle numerical value 160 (Fig. 5 and Fig. 5 A) was provided, image composer recomputated all orthogonal projection figure and they is presented at the normal place place.Icon maker 289,299 and 346 couples of icon 430A, 460A and 520 data recomputate, and all these icons are presented at the normal place place once more.The image that shows has anatomical structure and proofreaies and correct orientation.
Figure 13 A and Figure 13 B show the cross-sectional view with the similar heart shown in Figure 11 A and Figure 11 B.But, in Figure 13 A and Figure 13 B, imaging system service range storbing gate 416B and 417B and angle range line 412B, 413B, 445B and 446B, this is because the distal portions 402 of conduit 400 is positioned on the tissue surface 399 of left ventricle 394 at present.Imaging system shows top view 470B (as shown in Figure 14 C) based on the setting of the range gating door among Figure 14 A and Figure 14 B.
Figure 13 A and Figure 13 B show the distal portions 30 of the probe 12 that is arranged in right ventricle 386 and are positioned at the distal portions 402 of the ablation catheter 400 of left ventricle 394.As mentioned above, imaging system uses transducer array 42 to collect echo data and the orthogonal projection figure of generation as shown in Figure 14 A, Figure 14 B and Figure 14 C.Video display units shows orthogonal projection figure and relevant icon in the pre-position as shown in Fig. 7 and Fig. 7 A.
Particularly, Figure 14 A shows sectional view 420B and front view icon 430B.Front view 420B shows the distal end of catheter part 402 that is positioned on the tissue surface 399.Front view 420B also shows the Bicuspid valve 392 between left ventricle 394 and left atrium 390.The clinician can set the position that gate 416B and 417B and ROI indicate 415B.Front view icon 430B has shown array axis 432B and available preceding visual field 436B and actual preceding visual field 434B.Actual preceding visual field 434B is corresponding to the azimuth coverage that is limited by line 412B and 413B, and available preceding visual field 436B is corresponding to maximum azimuth coverage.Relation between actual preceding visual field 434B and the available preceding visual field 436B shows spacing adjusting 181 (Fig. 5 A).The selected numerical value (Fig. 5 A) of representing deflection angle adjusting 183 with respect to the array axis 432B of the preceding visual field 434B of reality.
Referring to Figure 13 A and Figure 14 B, imaging system also can produce left side view 450B by collect echo data on the selected elevation coverage by line 445B and 446B and R0I sign 448B drafting.Left side view 450B has shown the part and the distal portions 402 that is positioned on the left ventricle surface 399 of barrier film 388.Referring to Figure 13 B, left figure icon 460B shows available side-looking field 462B and actual side-looking field 464B, and actual side-looking field 464B is corresponding to the elevation angle that obtains image sector.The display scrolling that concerns between available side-looking field 462B and the actual side-looking field 464B is regulated 182 (Fig. 5 A).
Figure 13 C and Figure 13 D are the projections of human heart.Figure 13 D shows the distal portions 30 of probe 12 and is positioned at the top-sectional view of the distal portions 402 of the ablation catheter 400 on the heart surface.Figure 14 C has shown the C-scan projection top view 470B that is produced by the B-scan data in range gating door 416B and 417B, and has shown top view icon 490B.Top view 470B show be positioned at the surface near 399 distal end of catheter part 402 and the part of Bicuspid valve 392. Range gating door 416B and 417B and angle range line 412B, 413B, 445B and 446B define the area of top view 470B.Figure 14 C has also shown top view icon 490B, and top view icon 490B comprises rectangular array 492B and array axis 494B.Axis 494B represents the deflection angle of top view 470B with respect to the angle on the limit of rectangular area 492B.
Other embodiment is in following claim:

Claims (12)

1. transesophageal ultrasonography imaging system that is used for physiological tissue's imaging, it comprises TEE probe (12),
Described TEE probe comprises:
Elongated half flexible body (36) that has far-end (30),
Be connected to the flexure region (34) of the far-end of described elongated half flexible body,
Be connected to the distal tip (50) of the far-end of described flexure region,
Be connected to the probe handle (14) of the near-end of described elongated half flexible body, described probe handle comprises the register control (15) that is connected to described flexure region by described elongated half flexible body; With
Be in the matrix two-dimensional ultrasound transducer arrays of described distal tip;
Described TEE pops one's head in and is characterised in that,
Described matrix two-dimensional ultrasound transducer arrays (42) can be operated to the electronic guide wave beam on two planes more than volumetric region;
Distal tip (50) comprises the integrated circuit (62) of the element that is connected to described two-dimensional ultrasound transducer arrays.
2. transesophageal ultrasonography imaging system as claimed in claim 1 is characterized in that, distal tip also comprises the array backing (60) of the element back that is positioned at described two-dimensional ultrasound transducer arrays.
3. transesophageal ultrasonography imaging system as claimed in claim 1 is characterized in that, distal tip also comprises radiator (68), as the heat transfer effect of the heat that integrated circuit produced.
4. transesophageal ultrasonography imaging system as claimed in claim 1 is characterized in that, elongated half flexible body comprises the gastroscope pipe.
5. transesophageal ultrasonography imaging system as claimed in claim 1, it is characterized in that, described probe comprises the locking mechanism of jointly arranging with the attachment areas of this probe, and described locking mechanism is configured to be locked in position in described two-dimensional ultrasound transducer arrays after described array is with respect to the tissue regions orientation of being paid close attention to.
6. transesophageal ultrasonography imaging system as claimed in claim 1 is characterized in that, the element of described two-dimensional ultrasound transducer arrays is set to two subarrays (43,44).
7. transesophageal ultrasonography imaging system as claimed in claim 6 is characterized in that, also comprises a plurality of groups of interior preprocessors (220) that receive, and each the described group interior preprocessor that receives links to each other with the element of subarray.
8. transesophageal ultrasonography imaging system as claimed in claim 7 is characterized in that, receives in each group that preprocessor (220) is configured to postpone and in conjunction with the signal by the element of correlator array.
9. transesophageal ultrasonography imaging system as claimed in claim 1 is characterized in that, also comprises parallel beamformer (225), in response to the signal that the element by matrix two-dimensional ultrasound transducer arrays (42) receives, is arranged to synthetic simultaneously a plurality of received beams.
10. transesophageal ultrasonography imaging system as claimed in claim 1, it is characterized in that, also comprise picture system, in response to the signal that the element by matrix two-dimensional ultrasound transducer arrays (42) receives, be arranged in from the plane of delineation that extend on the plane of matrix two-dimensional ultrasound transducer arrays and produce one or more images.
11. transesophageal ultrasonography imaging system as claimed in claim 10 is characterized in that, described picture system works to produce a plurality of spaces different images; And also comprise orientation icon maker (289), be arranged to produce the display orientation icon of the relative orientation that shows described space different images.
12. transesophageal ultrasonography imaging system as claimed in claim 1, it is characterized in that, also comprise the picture system that is connected in described TEE probe, this picture system comprises the edge detector (302,322) that is used for the signal that receives in response to the element by matrix two-dimensional ultrasound transducer arrays (42).
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