CN1189217A - Portable ultrasound imaging system - Google Patents

Portable ultrasound imaging system Download PDF

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Publication number
CN1189217A
CN1189217A CN96195104A CN96195104A CN1189217A CN 1189217 A CN1189217 A CN 1189217A CN 96195104 A CN96195104 A CN 96195104A CN 96195104 A CN96195104 A CN 96195104A CN 1189217 A CN1189217 A CN 1189217A
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circuit
ultrasonic
delay
signal
time
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艾利斯·M·羌
史蒂文·R·布罗德斯通
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TeraTech Corp
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TeraTech Corp
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Priority to CN96195104A priority Critical patent/CN1189217A/en
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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
    • A61B8/54—Control of the diagnostic device
    • A61B8/546—Control of the diagnostic device involving monitoring or regulation of device temperature

Abstract

This portable ultrasound imaging system (10) includes a scan head (12) coupled by a cable 16 to a portable battery-powered data processor (14) and display unit. The scan head enclosure (12) houses an array of ultrasonic transducers and the circuitry associated therewith, including pulse synchronizer circuitry used in the transmit mode to time transmission of ultrasonic pulses and beam forming circuitry used in the receive mode to dynamically focus reflected ultrasonic signals returning from the region of interest being imaged.

Description

Portable ultrasound imaging system
Related application of the present invention
The application is a U.S. Patent application 08/599, the continuation application of 816 (applying date is on February 12nd, 1996) is 08/496,804 and this application is an application number, the applying date is the continuation application of 29 U.S. Patent application in June nineteen ninety-five, at this these two parts of patented claims is incorporated into for your guidance.
Technical background of the present invention
Conventional ultrasonic image-forming system generally includes the hand-hold scanning head, and this scanner head is by cable and rack-mount large-scale control and treatment display unit coupling.This scanner head generally includes a ultrasound transducer array, it with ultrasonic energy emissions to imaging region and receive the reflected ultrasound energy return from this zone.Transducer converts the ultrasonic energy of receiving to low level electric signal, and this electric signal is sent to processing unit by cable.This processing unit is used the synthetic signal from transducer of suitable beam-forming technology (as dynamic focusing), so that produce the image of area-of-interest.
Typical conventional ultrasonic image-forming system can have the transducer array of being made up of 128 ultrasonic transducers.Each transducer links to each other with its treatment circuit, and this circuit is positioned among the controlled processing unit.This treatment circuit generally includes drive circuit, so that accurately the timing driving pulse is sent to transducer to start the emission of ultrasonic signal in emission mode.The timing pip of emission is sent to scanner head along cable from the operator's console processing unit.In receiving mode, the wave beam of treatment circuit system form circuit will suitable time-delay introduce each from the low level electric signal of transducer so that signal dynamics focuses on, consequently produce accurate image successively.
Figure 1A has illustrated the imaging array 18 of N the piezoelectric ultrasonic transducer 18 (1)-18 (N) that uses in ultrasonic image-forming system.This piezoelectric transducer unit [18 (1)-18 (N)] array produces sound wave pulse, and this sound wave pulse enters imageable target (normally tissue district) or transmission medium with narrow beam propagation.This pulse is propagated with constant speed as spherical wave.Surveyed by same transducer array 18 or another receiving array with the form of return signal from imaging point P or from the echo of reverberator, and show in the mode of the position of pointing out reflection configuration P.
The echo that orders from P in the transmission medium arrives each transducer unit 18 (1)-18 (N) of receiving array after the different travel-times.The travel-time of each transducer unit is different, and this depends on the distance between each transducer unit and the some P.For typical ultrasound-transmissive medium, i.e. soft tissue, this is real, because suppose that wherein the velocity of sound is constant (or constant relatively) in these medium.Then the information of receiving is shown in the mode that indicates the reflection configuration position.
When two-dimentional B-scan, pulse can transmit along a plurality of sight lines shown in Figure 1A.If to echo samples, and with the amplitude of echo as luminance coding, a width of cloth gray level image just can be presented on the cathode-ray tube (CRT) so.Image generally includes 128 such sweep traces, and angle intervals is 0.75 °, thereby forms 90 ° sector image.Because the velocity of sound in water is 1.54 * 10 5Cm/sec is so once time is 208 μ sec back and forth for the degree of depth of 16cm.Therefore, obtain the needed times of data along 128 sight lines and come to 26.6msec.If other signal processor processes speed is enough fast in the system, be enough to the acquisition speed that keeps such, so just can produce two dimensional image with the speed that is equivalent to television video.For example, if the chest wall that the ultrasonoscopy instrument is used to see through between a pair of rib is observed reflective sound wave or backward scattering sound wave, so, heartthrob is imaging in real time.
Ultrasonic transducer is the linear array of piezoelectric transducer 18 (1)-18 (N) (transducer is half wavelength at interval usually) normally, and as controlled array, its elevation angle form is fixed, and its orientation form mainly is subjected to handle time-delay control.The beam radiation of conventional arrays (orientation) form mainly is controlled by a kind of like this mode, wherein, delay pulse imposes on each transducer unit 18 (1)-18 (N), so that is all sued for peace together at picture point P place from the energy of all transmitters, so that produce the beam shape that suits the requirements.So, needing the radiation emitted orientation diagram in order to produce along predetermined direction, delay circuit and each transducer unit 18 (1)-18 (N) need be combined.
Arrive seen in Figure 1B, for given position angle, two kinds of different radiation patterns can be arranged: a kind of is " single focusing " mode, and another kind is " interval focusing " mode.Single focus method uses the single pulse that focuses on, and this pulse focuses on the middle part of image line along specific sight line.In single pulse mode, the depth of focus of level orientation can change by circuit, but all remains unchanged for any predetermined direction.When focusing on operation in the interval, launch a plurality of pulses along every sight line (or direction), wherein each pulse is gone up at different depth (interval) and is focused on.For the multiple-pulse operation, transmitter array is focused on M focal region along each direction of scanning, promptly produces a series of (M) pulse, i.e. P 0, P 1..., P M-1, each pulse focuses on its corresponding scope R respectively 0, R 1..., R M-1These pulses produce according to the order that repeats, so that each M pulse is not to begin to overlook new direction to be exactly and inceptive impulse P after startup 0Correspondence repeats to overlook the series of current direction.For interval focusing mode, need programmable format delay circuit and each transducer unit in conjunction with to be created in the beam pattern that different focal regions focus on.
As previously mentioned, can use same transducer unit 18 (1)-18 (N) array 18 to receive the signal that returns.The energy waveform that originates from the reflected beam (being echo) of picture point arrives each transducer unit after through time-delay, this time-delay equals speed that the distance from the picture point to the transducer unit propagated in medium by signal wave be divided by (supposing that this speed is constant).Similar with emission mode, for each transducer unit, this time-delay is different.At each receiving transducer place, for any given degree of depth, the difference of these paths all should be compensated by the mode that will focus on from the reflected energy of specific picture point on each receiver.Time-delay at each receiving element place all is the function that distance from this unit to array center and sight line depart from the angle of array normal direction.Should be noted that the sound wave pulse that is produced by each transducer is not broadband signal and should represents with amplitude and phase place in ultrasonic range.
The operation that wave beam forms and focuses on relates to the summation of the scattering waveform that all transducers are observed, but in the process of summation, all waveforms must have different time-delays, so that they all will arrive according to the phase place and the amplitude of summation.Therefore, need wave beam to form circuit, this circuit can carry out different time-delays and can change time-delay in time at each passage.In given direction, when echo when darker tissue returns, receiving array changes its focusing continuously along with the degree of depth.This process is called dynamic focusing.
Fig. 2 A to Fig. 2 C is the schematic block diagram of three kinds of different conventional imagings of explanation and wave beam focal length technology.Non-programmable physics lens acoustic systems 50 is shown in Fig. 2 A, and it uses sound wave lens 51.Two kinds of dynamic focusings are shown in Fig. 2 B and Fig. 2 C respectively, and wherein relevant signal Processing electronic circuit all is used to finish time-delay in real time and phase place time-delay focusing function.Fig. 2 B explanation utilizes the time delays system 52 of time delays unit 53, and Fig. 2 C explanation utilizes the phase place delayed time system 54 of phase place delay unit 55.
In the no lens combination shown in Fig. 2 B and Fig. 2 C, signal processing unit 53,55 need be connected with each receiving transducer unit, thereby limits treatment channel, so that time delays is provided and makes the projectile energy from field measurement point focus on the formation image.Therefore, need wave beam to form circuit, this circuit can provide different time-delays on each treatment channel, and can further change time-delay in time.In predetermined direction, when echo when distance transducer unit array larger distance is returned, the focusing that receiving array changes it along with the degree of depth continuously is to finish dynamic focusing.
After received wave beam forms, in the mode of routine with this wave beam digitizing.The digital picture of each pulse of receiving all is a time series, and this time series is corresponding one by one with the ultrasonic energy that returns from the field measurement point as the function of distance on the orientation that forms at wave beam.Consecutive pulses is sent to different directions, is covered with from-45 ° to+45 ° the visual field.In some system,, use the mean value (being called lasting weighting (persistenceweighting)) that calculates by the time from the Continuous Observation data of same field measurement point in order to improve picture quality.
For example, in the ultrasonic image-forming system of under 2 to 5MHz frequencies, working, for the accurate path compensation that suits the requirements needs to provide electronic circuit up to the temporal resolution of the time-delay of 10 to 20 μ sec and submicrosecond level.Shown in Fig. 2 B, delay line and intrinsic delay function coupling, this delay function is the needed delay function of dynamic focusing in the lensless ultrasonic system.
More particularly, in a ultrasonic imaging demonstration system, the frequency of operation of this system is 5MHz and the transducer array be made up of 128 transducer units that are positioned at the half-wavelength center, for suitable time-delay is set, directly time-delay mechanism requires each treatment channel/transducer unit or comprises having 25nsec resolution and programmable 480 grades delay line of clock period, perhaps comprises having 480 grades of tapped delay lines that the 40MHz clock constitutes with programmable 480 to 1 selection of time switches.There are two problems relevant with this routine techniques.The first, simple speed change clock generator is not development as yet so far.The second, for N level tapped delay line, select relevant area and the N of circuit with tap 2Be directly proportional, so sort circuit need take a large amount of microwafer areas to realize the integrated morphology of tap.
Owing to produce the complicacy and the difficulty of conventional control circuit, can only integrated several time-delay structures few in number on a microwafer, so form function and just need a large amount of chips in order to finish multiunit dynamic beam.Therefore, the ultrasonic image-forming system neither one of prior art is to adopt direct time-delay mechanism, and is to use the approximation method of plane wave frequency mixer.In this approximation method, total time-delay is divided into two parts: utilize the fine setting time-delay of the approximate needs of plane wave frequency mixer analogue technique and utilize real thick delay line at interval to realize the time-delay of coarse adjustment.
According to plane-wave approximation, the method that realizes the fine setting time-delay can be to revise each phase place that receives the interchange ripple that treatment channel receives and the sound wave that each receiving transducer unit is received mixes with the out of phase of local oscillator, promptly receives in treatment channel generation at each and simulates phase shift.Specifically, Tn is desirable compensation delay, and T ' n is the approximation that Tn roughly quantizes, and by selecting to have the local oscillation at suitable phasing degree, makes expression formula cos (ω 0T+ Ω n(t)) Ω in nSatisfy expression formula Ω n(t)=ω 0(T ' n (t)-T ' n (t)).People will be appreciated that the phase place of one of its intermediate frequency (IF) sideband provides phase coherence in the middle of all treatment channel when T ' n time-delay is used in frequency mixer output.
Adopt capability of tap selector in the conventional equipment of above-mentioned technology, this capability of tap selector is received the down converter output of receiving in the tap of thick interval series connection delay line.This capability of tap selector is a multipoint switch basically, and it receives one of its numerous output terminals to its input.Provide an output terminal to each tap on the delay line.So the output of each frequency mixer can be received in the tap at the several thick intervals few in number on the delay line, and all taps output can coherently be sued for peace.But for the demonstration of 5MHz, if adopt the arrangement of above-mentioned single frequency mixer, this delay line needs the time-delay resolution that is lower than 1 μ sec.
In a word, the routine techniques of introducing so far all relates to the mixing (heterodying) of exporting by signal of selecting local oscillation frequency to finish to receive and oscillator, so that output frequency is reduced to intermediate frequency (IF) frequency.Then this signal through frequency reducing is added on another frequency mixer.By the suitable phasing degree of selecting second oscillator, the phase place of the intermediate wave that control mixing for the second time produces.Then, during the focusing scanning of each direction, second frequency mixer output is added on unique or the several at the most thick spaced tap of delay line by capability of tap selector.
Use above-mentioned approximation technique to be because the following fact is promptly utilized the technology that obtains easily, as Analogue mixer and RC network, can make image focusing, thereby obtain the image that a width of cloth more or less focuses on economically viable mode.Unfortunately, compare with desirable focusing (perfectly time-delay) situation, the frequency mixer method of approximation causes image the coordination inaccurate error and the loss of signal.
In order to realize function, modern ultrasonic system needs very complicated signal processing circuitry.For example, for forming, dynamic wave beam needs hundreds of time-delays and summing circuit.Moreover, for the depth information and the doppler information of two dimension are provided with the color flow motion video, need doppler processor pulse or continuous, and need wave filter in order to eliminate clutter.Each all needed arithmetic speed to surpass 10 during these were used, 000MOPS (1,000,000 computings MOPS=p.s.).7 attitude CMOS chips of prior art, each chip can only provide hundreds of MOPS, and each chip needs several watts of electric power power consumptions.Therefore, need hundreds of chips with conventional ultrasound machine of equipping, and consume hundreds of watts of electric power.Therefore, conventional system can only be assembled into the little operator's console of the big posture installation of standard.
Another shortcoming of conventional ultrasonic system is that the cable that connects scanner head and processes and displays unit and need is a complicated cable extremely, therefore also is unusual costliness.Because all in treatment bench, all must be sent to the treatment circuit system from scanner head from the low level electric signal of ultrasonic transducer to all wave beams formation Circuits System.Because it is so low consuming level, so that they are very responsive to noise, cross (talk) and loss.Adopt typical 128 transducer arrays that transducer causes, the cable between scanner head and processes and displays platform need comprise the low low-loss concentric cable of cross (talk) of 128 low noises.This cable needs very expensive material and very long built-up time, so very expensive.
The present invention's general introduction
The present invention relates to portable ultrasound imaging system and method.Imaging system of the present invention comprises the hand-hold scanning head, and this scanner head is connected with portable treatment circuit system by cable.Scanner head comprises a housing, comprises ultrasound transducer array in this housing, and this transducer sends to the interesting areas for the treatment of imaging with ultrasonic signal, receives from the ultrasonic signal of this interesting areas reflection and with the ultrasonic signal of receiving and converts electric signal to.Also be included in the wave beam that uses in the imaging system of the present invention in the scanner head housing and form Circuits System, it will merge the electronic image that becomes this interesting areas from the electric signal of ultrasonic transducer.The electronic image of this area-of-interest is sent to data processing and display circuit system by the interface and the cable of system, and this Circuits System utilizes this electronic image to produce the image of this area-of-interest.
In one embodiment, portable treatment circuit system is equipped with the kneetop computer form, this computing machine comprises an integrated keyboard, a PCMCIA standard modem card and a flat panel displays that is used for the transmitted image data, as active liquid crystal device matrix.Kneetop computer and a complete set of system can enough small and exquisite powered battery.So comprise that a complete set of system of scanner head, cable and computing machine is very light in carrying.The general assembly (TW) of this system is no more than 10 pounds.Comprise also that in scanner head inside Faraday shield makes it avoid extraneous radio frequency source interference with the electronic circuit of shielding scanner head.
In one embodiment, system also is included in an interface unit between scanner head and the kneetop computer.System cable no longer directly connects on computers, but is connected on the interface.Another cable is connected to interface unit on the computing machine.Interface unit is finished control, and signal/data processing function be can't help computing machine and finished.Reduced the total processing load on the computing machine like this.
In another embodiment, higher-quality image is presented on the cathode-ray tube display.In this embodiment, be sent to processor (as PC or kneetop computer) through cable from the signal of scanner head, this processor again with the cathode-ray tube display interface.Signal from scanner head is received by processor, and this signal of processor processing and generation are fit to the signal of demonstration, are transported to cathode-ray tube (CRT).
Supporting for the function that makes scanner head and ultrasonic image-forming system of the present invention, the multiple signal processing circuitry relevant with ultrasonic transducer is integrated on the little CMOS chip.For example, the used wave beam formation Circuits System of receiving of ultrasonic signal is introduced in independent time-delay just can be provided on a slice chip, can be used for 64 cell arrays.Therefore the system of 128 unit has only two chips.The pulse synchronization circuit system that is used to produce the transducer drive pulse also can be provided in chip.In addition, in emission mode, be used for driving the high-voltage driving circuit of transducer and the pre-amplification circuit and the gain control circuit that are used to adjust from the electric signal of transducer at receiving mode also can both be integrated in a slice chip.Also have, control circuit (as be used to select from the signal of transducer multiplexer circuit) and other this class control circuit also can both form on a slice chip.
In an embodiment preferred of the present invention, the CMOS technology that the signal processing circuitry in scanner head is pressed low power high speed is equipped with.System compares with custom circuit, and integrated circuit (IC) system can also adapt under lower voltage to be moved.Therefore, power that consumes in integrated circuit (IC) system and consequent thermal effect all are significantly less than the custom circuit system.In one embodiment, the general power that consumes in scanner head is lower than 2 watts.This allows the temperature of scanner head to remain on below 41 ℃.So low power consumption and temperature can be provided in the smaller scanner head housing circuit, and can not descend owing to thermal effect suffers any performance.The thermal effect that the patient who is checked also can not be harmful to.Because system only needs smaller power, so can also be with the powered battery that is arranged in data processor and display unit.
Just as discussed above such, each signal by each transducer reception of in ultrasonic system, independently delaying time and being introduced into the ultrasonic pulse of each independent transmission usually and representing reflected ultrasound energy.These are independently delayed time and are used to guarantee that the image of area-of-interest is suitably focused on.
The form of each transducer unit or the influence that scheme is subjected to array shape and the region shape that needs scanning are introduced in time-delay.For example, in phased array, for every sweep trace all the time-delay of different independent manipulation wave beams is introduced each pulse and (or) each return signal so that produce the image of the adequate focusing of arc area.
Linear array or camber line shape array normally flat or crooked.These arrays can be used to finish linear sweep, and the pattern of will delaying time uniformly in this pattern is introduced all transducers.For every sweep trace time-delay is the same.Crooked array has different time-delay schemes for every sweep trace.The present invention can also finish trapezoid area scanning.
In one embodiment, linear array is used for sub-hole (sub-aperture) scan method.For example, in this embodiment, transducer array can comprise 192 transducers that adjoin lining up a line.In sub-hole scan period, have only sub-fraction transducer (for example 64) to be used for producing and received signal.Transducer at the linear array two ends is used to finish the phase-array scanning method, so that produce crooked image area at keystone scanning district opposite end.Because the phased array method is used to the two ends of array, must to every independently sweep trace introduce different time-delay patterns.Between phased array, adopt linear sweep.Therefore, during the linear sweep of this method, one group of time-delay can be used for all sweep traces.So combining of the linear sweep at the phase-array scanning that keystone scanning embodiment of the present invention relates to regional two ends and middle part, zone.
In typical ultrasonic image-forming system,, the accurate signal path compensation needs to provide up to the time-delay of 10 to 20 μ sec and electronic circuit system with submicrosecond level temporal resolution for being provided.In embodiment preferred of the present invention, the time-delay that utilizes the charge-coupled image sensor technology this wide region to be provided and to have had fine-resolution by a programmable tapped delay line of twin-stage.The first order will be finely tuned time-delay and be introduced, and the coarse adjustment time-delay is introduced in the second level.Time-delay is subjected to tap clock frequency (tapping clock frequencies) control, compares with the coarse adjustment time-delay, and the clock frequency ratio of control fine setting time-delay is higher.In one embodiment, fine setting time-delay clock frequency is arranged to 8 times of ultrasonic signal frequencies, and the clock frequency of coarse adjustment time-delay is arranged to finely tune 1/10th of time-delay clock frequency.Clock frequency can separately be controlled and help changing ultrasonic signal frequencies, helps changing imaging depth.
This class device once had introduction at the U.S. Patent application of correspondence, they are respectively the patented claims of being submitted to by AliceM.Chiang that is entitled as " Integrated Beam Forming and FocussingProcessing Circuit for Use in Ultrasound System ", application number is 08/496,915; With the patented claim that is entitled as " Integrated DelayProcessing Circuit " that Alice M.Chiang submits to, application number is to be June 29 nineteen ninety-five the applying date of 08/496,463, two parts of applications.At this these two parts of patented claims are incorporated into for your guidance.
In one embodiment, ultrasonic signal frequencies can change to allow imaging on different depth.This can be accomplished by the inside adjustment or outside adjustment of transducer signal driving frequency.On the other hand, with regard to the frequency change of broad, system of the present invention can adapt to different scanner heads, and these scanner heads have the array of working under different frequencies.In addition, scanner head of the present invention can provide the setting that changes array according to the frequency of operation of needs.
In another preferred embodiment, delayed processing circuit utilizes single charge-coupled image sensor delay line, and this delay line has programmable input sampling selecting circuit.Programmable input sampling selecting circuit permission imaging signal sampling unevenly is loaded on the programmable delay line, so that the variable time-delay that needs to be provided.
In this embodiment, each delayed processing circuit comprises an input sampling circuit able to programme and a programmable delay unit.Selection scheme according to user's appointment, sample circuit able to programme is transformed into the simulated data sampling sequence of discrete time with the input waveform of continuous time and this sequence is loaded in the programmable delay unit, and the interval of this sequence both can be also can be uneven uniformly.Control circuit is included, provide programmable time-delay each selected sampled data.Summing circuit is merged to come in, calculate from the sampled data of the time-delay of each delay unit and, so that the image of focusing is provided.
In one embodiment, be used to control each control circuit of delaying time of taking a sample and comprise a counter and a memory circuit, this memory circuit can be a shift register, also can be memory circuit.Shift register utilizes the charge-coupled image sensor fabrication techniques, also can utilize other logical circuit technology.Before every sweep trace produced, memory circuit loaded with a series of data value, and these data value definition are used for the time-delay of each focus on the sweep trace.Under sampling clock control, the value of storing in the output of counter and the shift register compares one by one.The value of coupling causes extracting a sample of signal.Therefore, just can control the sampling time-delay by a plurality of suitable numerical value of storage in memory circuit (shift register).
In one embodiment, all right memory address value of shift register, level suitable in the programmable delay line is determined in this address, this depends on the sampling time-delay that is used to be scheduled to.This time-delay values of tap preferably is stored as a series of data bit, and these data bit are useful on the sampling time-delay value corresponding that provides above-mentioned.In one embodiment, two numerical value are merged into one 9 bit data word, and in delay line, 3 are used to the delay selection of taking a sample, and the time-delay tap of 6 delay lines that are used for is selected.In one embodiment of the invention, every sweep trace comprises 512 focuses.Therefore, shift register is one 512 grades 9 a shift register.Another kind of way is, 4 are used to the delay selection of taking a sample, and 7 taps that are used to delay time are selected, and cause using 512 grades 11 shift register like this.
In another embodiment, data word is compressed into 9, for more effective storage data create conditions.In this embodiment, be not to store each independently to delay time, but the difference of delaying time between the focus is adjoined in storage.The figure place that the figure place time-delay absolute value actual than storage that storing each first difference needs needs is lacked.In another embodiment, second difference, the difference of first difference of promptly adjoining, it is stored in each register.This need be less than 7.In order to handle each time-delay, processor of the present invention is read each difference, then it is added up to produce the actual time delay value, goes to control the sampling and the switching (sampling and tapping) of delay line with this value.In the first difference embodiment, use the one-level summation, finish and add up.Under the situation of storage second difference, use the secondary totalizer.
In one embodiment of the invention, can adopt and be called as sub-hole scan process.In this method, treatment circuit is shared by transducer, so that the treatment circuit sum is less than the transducer unit number.For example, array comprises 128 transducer units, has only 64 treatment channel.In this embodiment, adopt multichannel to handle, once only use the central part of 128 transducers whereby, i.e. " sub-hole " part.Adopt the effective transducer of multi-channel transmission channel arrangement to the signal transmission path of handling Circuits System.In one embodiment, once use 64 transducers, and have the passage of 64 treatment circuit systems to be they services.After first group of 64 transducer obtains view data, next group transducer is activated, to gather more data.Usually, adopt slip scan to handle, continuous group of each Unit 64 slips over a unit in this method, thereby causes sub-hole scanning area overlapping.In sub-hole scan period, adopt the processing of spatial window to reduce picture noise, promptly reduce the energy that obtains by sideband in the image rather than the main lobe of array response.Promptly can adopt the spatial window of dynamic change can use the constant spatial window of intercepting again.But, have found that the window ratio of intercepting is easier to realize.
In this embodiment, for the unit that every group is activated is provided with time-delay, in linear scan pattern, the storer of giving array location is downloaded in same group of time-delay.When the hole was mobile towards continuous group, the numeral of representing independent delay circulated effectively by the storer and the control circuit of each treatment channel.In other words, for first group of unit, the time-delay group that is numbered 1-64 is loaded into respectively among the treatment channel 1-64.For next group, time-delay group 1-64 is loaded into treatment channel 2-64,1 respectively.For next group again, time-delay 1-64 is loaded into treatment channel 3-64 respectively, 1-2, and the rest may be inferred.The multipath transmission delay data value of this rotation has improved efficient of the present invention widely, has significantly reduced because store the quantity of the required storer of all delay datas.Thereby the hardware quantity that needs has also reduced.
In another preferred embodiment that substitutes, adopt adaptive beam to form circuit and replace the twin-stage delay line, so that resolution on demand provides the time-delay that needs.In adaptive beam formation technology, the summing signal that the feedback circuit impression is received from tapped delay line, and produce a correction signal.This correction signal is being controlled the weighting that wave beam forms each multiplier in the Circuits System, so that adjust summing signal and clutter and the interference (clutter and interference) eliminated from image.
As mentioned above, in wave beam formation circuit dynamic focusing with after to the processing of suing for peace from the signal of ultrasonic transducer, the signal of summation is sent to the data processing and the display subsystem of imaging system by system cable.Comprise Circuits System such as demodulation, recording compressed and scan conversion in the data process subsystem, wherein the scanning conversion circuit system is used for the polar coordinate transform of the ultrasonic signal the received coordinate that meets at right angles, and further handles being fit to, as showing.Scan conversion method of the present invention provides higher-quality image, and the Circuits System that needs is much simpler than prior art.
In the scan conversion of conventional system, in that (x, y) numerical value of each point will (r, θ) numerical value of immediate four unit on the array calculates with simple linear interpolation according to polar coordinates on the coordinate system.This finishes by following method, promptly use finite state machine to produce (x, y) transversal scanning (traversals), use bidirectional shift register to preserve (r, θ) data sampling and use a large amount of Digital Logic and storage unit control and treatment process and guarantee correct (r, θ) data sampling is used for interpolation in the correct time and becomes (x, y) data are because (x, y) data point is asynchronous reception.
In the present invention, use Digital Theory mode (number-theoretic scheme) by natural order produce reliably (x, y) grid transverse path (gridtraversal path), promptly (r, just utilize them when θ) taking a sample, thereby reduced the complicacy and the cost of hardware.For the medical data of reality, this provides greater flexibility and better authenticity, because its allows the transversal scanning (traversals) of array of designs, so that they do not expose the profile of factitious image repetition.The method that the present invention adopts provides greater flexibility, has multiple by (x, y) active path of array according to the method.Therefore, whole advantages has been to adopt different ultrasonic scanning frequencies, thereby obtains different imaging depths.
After scan conversion, it is carried out aftertreatment in view data according to the final display format of its expection.For example, can handle count wordization and format of data in order on display, to show.In addition, (x, y) data value can be submitted to the video compress subsystem, and this subsystem packed data is to allow by modulation-demodulation technique or other known mechanics of communication data being sent to remote station.
Ultrasonic image-forming system of the present invention also allows to make motive target imaging by the Doppker processing subsystem.The data that form Circuits System from wave beam are sent to the pulse Doppler processor, are used for the data of motive target imaging with generation.For example, utilize the pulse Doppler processor can produce the mobile distributed image of colour that blood flow is crossed tissue.
In another preferred embodiment, data processing and display unit can be the unit of a small battery powered.It can hand or be worn on the user or be placed in user's the pocket on one's body.Combine with hand-hold scanning head of the present invention, this will make the ultrasonic system of the present invention fully can be portable.
Ultrasonic image-forming system of the present invention has been compared some advantages with the existing conventional system.Because numerous signal processing circuitries is integrated on the little chip of several piece, so signal Processing can be carried out in scanner head.Because transducer is near the treatment circuit system, the loss of signal reduces significantly.This causes in the performance of having improved system aspect formation high resolving power, the high quality graphic widely.Have again, because signal summation also finishes in scanner head, so only need one or several considerably less cable conductors that picture signal is sent to the treatment circuit system.The cable that required cable all uses well below conventional system aspect complicacy and expensive degree.
The portability of picture system of the present invention also is very important advantage.As mentioned above, this system comprises small and exquisite hand-hold scanning head and cable, and processes and displays unit that can be portable, as kneetop computer or the laptop computer with integrated liquid crystal display or other flat-panel monitor and keyboard.It can use powered battery, therefore is easy to carry, and the people who keeps a close eye in distant for needs also can promptly make diagnosis.By using video data compression technology of the present invention, the view data of far gathering can be sent to hospital by modulation or wireless phone or other known methods and judge.Processing instruction can be passed to the operator then, the operator can directly give patient treatment on the spot.
Another embodiment preferred of the present invention relates to foregoing circuit and method is used for two-dimentional transducer array equipment.For example, this transducer device be provided at the focusing in second dimension and can utilize in a plurality of linear arraies row with capable between thicker interval.
Another embodiment preferred of the present invention relates to the purposes of ultrasonic transducer equipment in stethoscope.This system provides audio-frequency information and ultrasonic imaging ability to the user.
Another embodiment preferred of the present invention relates to the purposes of ultrasonic transducer equipment in surface reparation (plastic operation).By sending and reception information between the rib that transducer device is positioned at the patient, this equipment can be used for the supervision of heart.
Treatment circuit system that another embodiment preferred of the present invention will here be introduced and control circuit system merging are placed on the inner ultrasonic probe or the end of imaging catheter.This provides more flexible more cheap imaging probe, and it is useful for diagnosis and processing.
Brief description of drawings
Above-mentioned target of the present invention and other target, feature and advantage will know more that from the narration of with reference to the accompanying drawings embodiment preferred of the present invention being done more specifically identical in the accompanying drawings reference symbol refers to same parts in all accompanying drawings.Accompanying drawing there is no need to make in proportion, focuses on illustrating principle of the present invention.
Figure 1A and Figure 1B are illustrated respectively in the block scheme of the conventional imaging array that uses in the ultrasonic image-forming system, and in interval focusing mode the monopulse pulse transmitting pattern relevant with multiple-pulse.
Fig. 2 A to Fig. 2 C represents three kinds of different conventional imagings or wave beam focusing technology respectively, and they relate separately to optical lens, time delays and phase place time-delay operation.
Fig. 3 is the synoptic diagram of the preferred embodiment of ultrasonic image-forming system of the present invention.
Fig. 4 is the functional-block diagram of the preferred embodiment of ultrasonic image-forming system of the present invention.
Fig. 5 is the functional-block diagram of the preferred embodiment of ultrasound scanhead of the present invention.
Fig. 6 represents the operator's block diagram according to the array of wave beam formation of the present invention and focus circuit.
Fig. 7 represents the more detailed operator's block diagram according to the array of wave beam formation of the present invention and focus circuit.
Fig. 8 represents operator's block diagram of an alternate embodiment of the present invention, and wherein each wave beam formation circuit and focus circuit are all incorporated an exclusive circuit into.
Fig. 9 represents the schematic block diagram according to the exemplary scheme of the exclusive circuit of the present invention's use.
Figure 10 represents operator's block diagram of another alternate embodiment of the present invention, and wherein each wave beam formation circuit and the selected output of focus circuit all impose on multiplier circuit separately.
Figure 11 represents operator's block diagram of an alternate embodiment of the present invention, and wherein a large amount of wave beam formation circuit and focus circuit are by the emission mode job-shop.
Figure 12 is the functional-block diagram that forms the preferred embodiment of Circuits System according to adaptive beam of the present invention.
Figure 13 represents wherein to adopt sampling selecting circuit able to programme and programmable delay circuit according to the schematic block diagram of an alternate embodiment of the array of wave beam formation of the present invention and focus circuit.
Figure 14 A represents the synoptic diagram according to the exemplary embodiment of the sampling selecting circuit able to programme that is subjected to storer control of the present invention's use.
The sequential chart of sampling selecting circuit shown in Figure 14 B presentation graphs 14A.
Figure 15 represents according to storer of the present invention and the detailed block scheme of the preferred alternate embodiment of control circuit.
Figure 16 represents that wave beam shown in Figure 13 forms the schematic block diagram of circuit embodiment, wherein adopts charge-coupled image sensor programmable delay line.
Figure 17 is according to storer of the present invention and the detailed block scheme of another preferred alternate embodiment of control circuit.
Figure 18 is according to storer of the present invention and the detailed block scheme of another preferred alternate embodiment of control circuit.
Figure 19 represents the block scheme of alternate embodiment of the present invention, and wherein the selected output of each wave beam formation and focus circuit imposes on multiplier weighting circuit separately respectively.
Figure 20 represents the block scheme of alternate embodiment of the present invention, wherein the multiplier weighting circuit is placed on the input end of delay unit.
Figure 21 represents the block scheme of alternative arrangements of the present invention, and finite impulse response (FIR) (FIR) wave filter that wherein is used for the time domain interpolation is placed in the back of delay unit.
Figure 22 represents the block scheme of finite impulse response filter equipment, and wherein the fixed weighting multiplier is used to import sample interpolation.
Figure 23 represents the block scheme of another kind of finite impulse response filter equipment, and multiplier wherein able to programme is used to input from the sample interpolation.
Figure 24 is the synoptic diagram of explanation scan conversion process of the present invention.
Figure 25 is the functional-block diagram according to pulse Doppler processing unit of the present invention.
Figure 26 is the block scheme that adopts the colored flow distribution chipset of dual pulse Doppler processor according to the present invention.
Figure 27 is the functional-block diagram of the preferred alternate embodiment of ultrasonic image-forming system of the present invention.
Figure 28 is by the butt that curve ratio is used at sub-hole sweep interval according to the present invention truncate constant spatial window and dynamic spatial window.
Figure 29 is two kinds of image display format synoptic diagram that can supply the user to select that use in ultrasonic image-forming system of the present invention.
Figure 30 A is according to the graphic extension of the present invention to concerning between ultrasonic transducer linear array and the rectangular scanning district.
Figure 30 B is the graphic extension that concerns according between the scanning area of the present invention to ultrasonic transducer curve pattern and bending.
Figure 30 C is according to the graphic extension of the present invention to concerning between ultrasonic transducer linear array and the keystone scanning district.
Figure 30 D is the graphic extension in phase shift array scanning district.
Figure 31 is the block scheme according to circuit board of the present invention.
Figure 32 is the partial schematic sectional view according to an embodiment of linear sweep head of the present invention.
Figure 33 is that the side of the scanner head of Figure 31 is cutd open synoptic diagram.
Figure 34 is the partial schematic sectional view that adopts the scanner head of transducer curved arrays according to the present invention.
Figure 35 is the cross-sectional schematic according to the inner ultrasonic probe of the present invention.
Figure 36 is a top level flow, and its explanation is used to control the software logic flow process of operation of the present invention.
Figure 37 is the elevation drawing according to transducer two-dimensional array of the present invention.
Figure 38 is according to the stethoscopic graphic extension of ultrasonic electronic of the present invention.
Figure 39 A and 39B are the graphic extensions according to ultrasonic transducer orthopedic systems of the present invention.
Figure 40 A and Figure 40 B are the graphic extensions according to ultrasonic probe of the present invention or conduit.
Detailed description of the present invention
Fig. 3 is the synoptic diagram of ultrasonic image-forming system 10 of the present invention.This system comprises hand-hold scanning head 12, and it and portable data are handled and display unit 14 couplings, and this unit can be a laptop computer.In addition, data processing and display unit 14 can comprise and the personal computer of the cathode ray interface tube that is used to show ultrasonoscopy or other computing machine.Data processing and display unit 14 can also be small and light monolithic cells, and it is small enough to be handed or wear or carry by the user.The volume of hand-held display is less than 1000cm 3, and preferably less than 500 cm 3Although shown in Figure 3 is the external scan head, scanner head of the present invention also can be the inner scanning head, and it is fit to insert health by tube chamber and makes in-vivo imaging.For example, probe can be used for spying upon in orifice of the stomach (or heart) imaging head (transesophgealprobe).
Scanner head 12 is connected with data processor 14 by cable 16.In alternate embodiment, system 10 comprises interface unit 13 (the with dashed lines frame table shows), and it plays coupling between scanner head 12 and data processing display unit 14.Interface unit 13 preferably comprises controller and the treatment circuit system that comprises digital signal processor (DSP).Interface unit 13 finish the signal processing tasks that needs and with signal output offer data processing unit and (or) scanner head.
Hand-held housing 12 comprises transducer portion 15A and processing section 15B.Transducer portion 15A is maintained at 41 ℃ below the temperature, so that this part case temperature that contacts with patient skin is no more than this temperature.The temperature of processing section 15B is no more than second higher temperature, and this temperature is preferably 50 ℃.The volume of hand-hold scanning head is less than 1000cm 3, and preferably less than 500cm 3, and along the length of its main shaft less than 20cm.
Fig. 4 is the functional-block diagram of an embodiment of ultrasonic image-forming system 10 of the present invention.As shown in Figure 4, scanner head 12 comprises ultrasound transducer array 18, and it is imaging target 11 (as tissue) that this array is transmitted to interesting areas with ultrasonic signal, and receives the ultrasonic signal that returns from the imaging target.Scanner head 12 also comprises the driver circuitry 20 and the pulse synchronization circuit system 22 of transducer.Pulse synchronization circuit system 22 is with the pulse transmission of a series of accurate timings and the time-delay high-voltage drive circuit in the driver 20.When driver 20 was received each pulse, the high-voltage drive circuit was activated, and high-voltage driven signal is sent to each ultrasonic transducer in the ultrasound transducer array 18, to activate transducer ultrasonic signal was transmitted to imaging target 11.
Ultrasonic echo by 11 reflections of imaging target is surveyed by the ultrasonic transducer in the array 18.Each transducer is transformed into electric signal with the ultrasonic signal of receiving, gain control (TGC) Circuits System 25 that is sent to pre-amplification circuit 24 and changes in time.Pre-amplification circuit 24 will be arranged on from the electrical signal levels of transducer array 18 on the level that is fit to subsequent treatment, form circuit 26 (below introduction) and temporal gain control circuit system 25 is used to compensate the decay that sound pulse causes when seeing through tissue and drive each wave beam, to produce line image.Be sent to wave beam through the electric signal of adjusting and form Circuits System 26, this Circuits System is introduced each signal of receiving with the difference time-delay, this signal dynamics is focused on, so that set up accurate image.Form signal of the summed one-tenth of signal that circuit 26 is delayed time by wave beam, this signal is sent to processes and displays unit 14 by cable 16.Being used for that the wave beam formation circuit 26 of the signal of receiving and the details of delay circuit and the pulse that is produced by impulsive synchronization device 22 are introduced in the difference time-delay will go through below.
In a preferred embodiment, the signal of process dynamic focusing and summation is sent to A/D converter 27, and this converter is with the summing signal digitizing.Then, digital signal is sent to memory buffer 29 and 31 from A/D converter 27 through cable 16.It should be noted that in the alternate embodiment that the simulating signal with summation directly transmits by cable 16 without A/D converter 27.In order to simplify, A/D converter 27 is saved from further instruction.
From the data of memory buffer 31 by separating the scanning conversion circuit system 28 that logical compressed Circuits System 41 delivers in the data processing unit 14 that is in harmonious proportion.The digitized signal data that scanning conversion circuit system 28 will form Circuits System 26 from wave beam from polar coordinates (r, θ) be transformed into rectangular coordinate (x, y).After conversion, the rectangular coordinate data are sent to back level signal Processing 30, and data are formatted there, so as show on the display 32 and (or) compression in video compression circuit system 34.Video compression circuit system 34 will be described in detail below.
Be sent to doppler processor 36 phase shift or continuous in the data processing unit 14 from the digitized signal data of memory buffer 29.Phase shift or continuous doppler processor 36 produces the data of the imaging target tissue 11 (as blood) that is used to move.In the embodiment that preferred band phase shift Doppler handles, produce the color flow cardon.Phase shift doppler processor 36 will send scanning conversion circuit system 28 to through the data that it is handled, and the polar coordinates of data are transformed into rectangular coordinate there, to be fit to demonstration or video compress.
Control circuit preferably adopts the form of microprocessor 38, and it is controlling the operation of ultrasonic image-forming system 10.The difference time-delay of impulsive synchronization device 22 and wave beam formation Circuits System 26 is introduced in control circuit 38 controls through storer 42 and control line 33.In one embodiment, the difference time-delay is introduced by programmable tap charge-coupled image sensor delay line, will introduce in detail below.These delay lines are stored in the Data Control in the storer 42.Microprocessor 38 control downloads to impulsive synchronization device 22 and wave beam with coarse adjustment and fine setting delay line tap data from storer 42 and forms online chip memory the Circuits System 26.In another embodiment, time-delay is controlled by the delayed processing circuit system, and this Circuits System comprises programmable input sampling circuit, and this circuit and the coupling of programmable delay unit will be introduced below in detail.
Microprocessor 38 is gone back control store 40, and this memory stores is by the data of phase shift doppler processor 36 and 28 uses of scanning conversion circuit system.Be to be understood that storer 40 and 42 can be that a storer also can be a plurality of memory circuitries.Microprocessor 38 also with back level signal processing circuitry 30 and video compression circuit system 34 interfaces, to control their functions separately.Packed data introducing in detail below video compression circuit system 34 resembles shows there and analyzes so that allow that view data is sent to remote station through transmission lines.Transmission lines can be modulation communication line or wireless phone communication line or other known communications service.
Portable ultrasound imaging system 10 of the present invention is by battery 44 power supplies.The primary voltage output of battery 44 drives an adjustable power supply 46, and this power supply is subsystem power supply all in the imaging system 10, comprises to the subsystem in the scanner head and powering.Therefore, the power of supply scanner head provides through cable 16 from data processing and display unit 14.
Fig. 5 is the detailed block scheme of a scanner head embodiment of ultrasonic image-forming system 10 of the present invention.As mentioned above, scanner head 12 comprises a ultrasound transducer array, in Fig. 3, they are marked into 18 (1), 18 (2) ..., 18 (N), wherein N is the sum of transducer in the array, normally 128.Each transducer 18 (1)-18 (N) and the coupling of treatment channel 17 (1)-17 (N) separately.
Each treatment channel 17 (1)-17 (N) comprises impulsive synchronization device 22 (1)-22 (N) separately, these impulsive synchronization devices will sensitizing pulse regularly offer high-voltage drive circuit 20 (1)-20 (N) separately in emission mode, and these high-voltage drive circuit offer separately transducer 18 (1)-18 (N) with drive signal.Each treatment channel 17 (1)-17 (N) also comprises filtering pre-amplification circuit 24 (1)-24 (N) separately, these amplifying circuits comprise voltage clamp circuit, will amplify from the signal of transducer 18 (1)-18 (N) and signal voltage is limited on the suitable level in receiving mode.The level of Bian Dong gain control circuit system 25 (1)-25 (N) control signal in time, and wave beam forms Circuits System 26 (1)-26 (N) is finished signal by each signal is introduced in the difference time-delay dynamic focusing.The output that forms circuit 26 (1)-26 (N) from wave beam is in summing junction 19 summations, and to produce the signal of last focusing, this signal is sent to data processing unit 14 through cable 16 and does next step processing.
In the present invention, wave beam forms and an embodiment of focus circuit 26 can be that they are integrated on a slice microwafer, and the charge-coupled device (CCD) tapped delay line that utilizes cascade provides independently coarse adjustment time-delay and fine setting time-delay, thereby causes existing wide reference time delay that trickle temporal resolution is arranged again.This wave beam of the present invention forms system implementation plan and is known as charge-domain processing (CDP) Circuits System in the text, this embodiment comprises a large amount of treatment circuits, in receiving mode, for these circuit of image of producing focusing make signal lag with the method for difference, these signals are as the representative from the received image waveform of ultrasonic energy of target reflection.In emission mode, make signal lag in order to produce directed these treatment circuits of focus beam with the method for difference, to be preparations be transmitted to target as ultrasonic energy by the array 18 of transducer 18 (1)-18 (N) to these signals.
Each treatment circuit comprises first delay line, and this delay line has a large amount of delay units, and in receiving mode, these unit can receive the image waveform and they are become sampled data (as charge packet).In emission mode, first delay line receives imaging signal and they is become sampled data (as charge packet).The selection control circuit can be in order to read sampled data from first delay unit of the first selected delay line and to work, so that corresponding to the first selected delay time of resolution of delaying time for the fine setting that adapts to image waveform or imaging signal.Second delay line with a large amount of delay units can be experienced the sampled data from the first selected delay unit.Control circuit further can be read sampled data from second delay unit of selected described second delay line, so that corresponding to the second selected delay time of resolution of delaying time for the coarse adjustment that adapts to image waveform or imaging signal.
In receiving mode, in order to produce the image of focusing, provide summing circuit, this circuit will be sued for peace from the sampled data of each second selected delay unit in each treatment circuit.In emission mode, output circuit is provided, this circuit will be transformed into the signal of representing directed focus beam from the sampled data of each second selected delay unit in each treatment circuit.
Wave beam form and focus on operation relate to form all observed waveforms of transducer unit and.But, in this summation process, must waveform be lagged behind with difference method, so that they all arrive summing circuit 19 (see figure 5)s by phase place.Therefore, forming circuit 26 according to each wave beam of the present invention all provides different time-delays and further changes this time-delay in time on every treatment channel.The signal of suing for peace by phase place for the signal that produces focusing is sent to data processing and display unit 14 subsequently.
For each nominal direction of scanning, the information that is received by transducer unit in the array 18 (k) mainly is to change with k with respect to first transducer unit 18 (1) required difference time-delays, and for the function do by a small margin correction of correction depth focus as the time.The overhead control of time-delay may relate to very trickle temporal resolution and big reference time delay.But, form direction for selected wave beam, realized one group of time-delay by the time-delay of the coarse adjustment in each passage with combining of fine setting time-delay, thereby make the coarse adjustment time-delay in each passage do approximate compensation, and the fine setting of each passage time-delay make focusing function and the function that the result finely tunes is once more proofreaied and correct in coarse adjustment and combine to direction.
Form an embodiment preferred of Circuits System 26 according to wave beam, this embodiment is shown in Fig. 6 with operator's block diagram form, each wave beam forms circuit 26 and is arranged at respectively in the predetermined passage among the parallel treatment channel of N bar 17 (1)-17 (N), one of the transducer unit 18 (1)-18 (N) of each array.Each wave beam forms the tapped delay line 56 (1)-56 (N) that circuit 26 comprises cascade, 58 (1)-58 (N).Each circuit 26 is as the signal (see figure 3) of input reception from temporal gain control circuit 25.First delay line 56 in every passage will be finely tuned time-delay and be offered the signal that it receives, and second delay line 58 of cascade provides the coarse adjustment time-delay.Every the fine setting delay line all has supporting programmable tap to select circuit 57 (1)-57 (N), and every coarse adjustment delay line all has programmable tap to select circuit 59 (1)-59 (N), and the two will be introduced in more detail.Tap selects circuit to influence variable delay time as the function of tap position.
At circuit 26 duration of works, the signal that each transducer unit 18 is received is continuously delivered to the input end of the treatment channel 17 of its correspondence.The input signal of delivering to each treatment channel is transformed into the sampled data sequence, and the initial fine setting tapped delay line 56 that passes through is separately propagated.According to the preferred embodiment of the invention, fine setting 56 and 58 two tapped delay lines of coarse adjustment all are the charge-coupled image sensor tapped delay lines.The programmable charge-coupled image sensor tapped delay line of demonstration once had introduction in people's such as Beynon " Charge-Coupled Device and TheirApplications " (McGraw-Hill (1980)), at this it is incorporated into for referencial use.Utilize in the demonstration structure of treatment circuit 26 of charge-coupled image sensor delay line at this, the input signal of each treatment channel is transformed into the charge packet sequence, subsequently by fine setting and the propagation of coarse adjustment delay line.
In the predetermined moment (it depends on the tap position that system 10 is selected), no matter whether the sampling of time-delay destroy information (destructively), all is that selected tap is read from fine setting delay line 56.The sampling of time-delay is by the front end of the coarse adjustment delay line 58 of input correspondence successively.Then, selected time-delay sampling is propagated by the coarse adjustment delay line, and the information of whether destroying all reads from suitable tap position once more, and this tap position is corresponding to the delay time of being scheduled to according to ultrasonic image-forming system 10 operation assignment.Simultaneously summed circuit 19 summations of sampled data of reading from the coarse adjustment delay line of every treatment channel, thus beamformer output formed.
Referring now to Fig. 7, this is the more detailed block scheme that wave beam forms Circuits System 26 (1)-26 (N) among Fig. 5 and Fig. 6.Such just as graphic extension, the programmable tap that is used to finely tune delay line selects each circuit in the middle of the circuit 57 (1)-57 (N) to comprise that all fine setting tap separately selects circuit 60 (1)-60 (N) and finely tune tap selection memory 62 (1)-62 (N).Equally, the programmable tap that is used for the coarse adjustment delay line selects in the middle of the circuit 59 (1)-59 (N) each circuit to comprise that all coarse adjustment tap separately selects circuit 64 (1)-64 (N) and coarse adjustment tap selection memory 66 (1)-66 (N).
Form the circuit embodiment preferred according to wave beam, fine setting has different clock speeds with the coarse adjustment delay line.Therefore the clock speed of fine setting delay line is higher than the coarse adjustment delay line, and it is much meticulousr than the coarse adjustment delay line to finely tune the delay time that delay line can provide.For example, in a demonstration structure, each circuit 26 has 32 grades of fine setting tapped delay lines, and its clock frequency is 40MHz, and the clock frequency of 32 grades of coarse adjustment tapped delay lines is 2MHz.The circuit of Gou Chenging can provide the time-delay up to 16 μ sec like this, and programmable time-delay resolution is 25nsec..Otherwise people will appreciate that if only use a delay line, so, it will need 640 grades of time-delays.In addition, because the present invention forms the delay line structure that adopts cascade in the circuit at wave beam, 64 grades of local storagies of 5 bit wides just are enough to provide the dynamic focusing function that is fit to the 15cm degree of depth.But,, needs 640 bit wides are taken advantage of 1280 grades of long local storagies if adopt a delay line structure.
Form circuit 26 run durations at wave beam independently, when receiving each echo, change the tap of fine setting delay line continuously through storer 42 (see figure 4)s, so that dynamic focusing to be provided by microprocessor 38.The fine setting tap selects circuit 60 to be used to select to finely tune the tap position that needs in the delay line 56 with the form of digitizing demoder with part fine setting tap selection memory 62.For example, microprocessor instruction storer 42 downloads data word to storer 62, offers with the digitized address that will represent selected tap position and selects circuit 60 so that decoding.Subsequently, select circuit 60 to carry out from selected tap extracted data sampling.In exemplary embodiment, 5 demoder is used to provide 32 kinds of taps to select.
The tap position of coarse adjustment delay line 58 was once set before each echo returns and is no longer changed during each orientation observation.The same with fine setting delay line operation, coarse adjustment tap selection circuit 64 is used to select the tap position that needs in the coarse adjustment delay line with the form of digitizing demoder with local coarse adjustment tap selection memory 66.
Fig. 8 represents that wave beam of the present invention forms operator's block diagram of the alternate embodiment of circuit 26, wherein each circuit comprises exclusive circuit 70 (1)-70 (N) separately, and this circuit selects circuit 60 (1)-60 (N) to produce a tap setting signal for each fine setting tap.When the tap setting signal was provided for fine setting tap selection circuit, tap selected to be fixed on last tap place (being focus) of fine setting tapped delay line, so the dynamic focusing function can not be moved.This operation is controlled by imaging system on the spot, and for example, imaging point is leaving on certain distance of transducer unit, and this distance need not just energy imaging of accurate fine setting time-delay.By this way, reduce the capacity of fine setting tap selection memory 62.
Exemplary embodiment according to an exclusive circuit 70 of the present invention is shown in Fig. 9.When operation, when microprocessor 38 is provided with height (level) to exclusive circuit, digitized data from storer 62 will be by the CMOS transistor of conducting, and the transistor reverser that is determined selects circuit (demoder) 60 that input is provided for suitable tap, so that realize the dynamic focusing function.Otherwise when to exclusive circuit low (level) being set, turn-on transistor lost efficacy, so reverser output will be latched in last address of storer, i.e. last tap position.
1.2 μ m CCD/CMOS manufacturing process (being provided by Orbit Semiconductor Inc.) are provided, and the sample that 10 passage wave beams of fine setting/coarse adjustment time-delay structure design that foundation is above-mentioned form microwafer has created.Owing to the closeness of every fine setting and coarse adjustment delay line, and because the simplification of the control circuit corresponding with it, the suitable wave beam that will be used for 64 unit receiver array of this method forms electronic circuit and is integrated in a slice microwafer.
Wave beam in this embodiment forms in the microwafer sample, and each treatment circuit comprises the programmable tap delay line (each 16 grades long) of two cascades, two 64 CMOS demoder and 4 * 64 the local storage that is used to store tap position.This sample is made of 10 treatment channel, and every passage all comprises the treatment circuit of the present invention that is produced on a slice silicon microwafer.Each treatment circuit can provide the programmable delay up to 10 μ sec, and time-delay resolution is 25nsec..Wave beam forms the chip operation, causes the echoed signal of receiving with given range resolution at each observed bearing angle transducer unit from picture point to take a sample by the treatment channel of correspondence.Each treatment circuit offers desirable compensation delay each return signal of receiving.Then, all time-delay output is summed, forms the picture point of the i.e. focusing of a wave beam.The chip area supporting with each treatment channel has only 500 * 2000 μ m 2Therefore, the dynamic beam that is used for 64 unit receiver array forms electronic circuit and can be integrated in a slice microwafer, and area of chip has only 64mm 2, compare this with conventional device and be equivalent to size and reduced by 3 to 4 orders of magnitude at least.
Fine setting of the present invention/coarse adjustment tap design is fit to provide 12 μ sec time-delay with the resolution of 25nsec on the charge-coupled image sensor tapped delay line that adopts the twin-stage connection.Specifically, this design comprises 16 grades long first delay line, and its clock frequency is 40MHz; And 32 grades long second delay line, its clock frequency is 2MHz.The simplicity of short delay line and the tap circuit relevant with these short delay lines allows all image generation electronic circuits all are integrated on a slice chip.A slice chip just can be finished the electron focusing function of 128 cell arrays, and compares with conventional device and will reduce two aspect chip area, power consumption and the weight more than the order of magnitude.
Figure 10 represents operator's block diagram of another alternate embodiment of wave beam formation Circuits System 26 among the present invention, and wherein the selected output of every coarse adjustment delay line 58 (1)-58 (N) offered multiplier circuit 80 (1)-80 (N) separately earlier before sending summing circuit 19 to.In U.S. Patent application, once introduced and be fit to the demonstration multiplier that above-mentioned wave beam forms the use of circuit embodiment, this application is submitted to February 10 nineteen ninety-five by Alice M.Chiang, be entitled as " Single-Chip Adaptive Filter Utilizing UpdatableWeighting Techniques ", application number is 08/388,170, at this its content is incorporated into for your guidance.
The structure of multiplier 80 be fit to be used the side lobe reduction technology, as known Hamming weighting or coding are incorporated into receiving array, with the level of reduction sideband, obtain high-quality image.Similar with embodiment shown in Figure 8, exclusive circuit 70 (1)-70 (N) can be included combines with each wave beam formation circuit 26 (1)-26 (N), so that the locking of the tap chosen position of control fine setting delay line 56 (1)-56 (N).Conventional side lobe reduction and Hamming weighting technique once had introduction, " Acoustic Waves:Device, Imaging, the and Analog Signal Processing " of Gordon S.Kino for example, Prentice-HallInc. incorporate its content for your guidance at this (1987).
Figure 11 is illustrated in the twin-stage connection tap charge-coupled image sensor delay line that uses in the impulsive synchronization device 22 (1)-22 (N), and it will be delayed time to introduce and independently transmit in the emission mode of ultrasonic system 10 of the present invention.Each impulsive synchronization device circuit 22 (1)-22 (N) comprises tapped delay line 56 (1) '-56 (N) of two cascades ' and 58 (1) '-58 (N) '.First delay line 56 ' in every treatment channel will be finely tuned time-delay and be offered armed signal, and second delay line of cascade provides the coarse adjustment time-delay.Every the fine setting delay line has supporting fine setting tap able to programme to select circuit 60 (1) '-60 (N) ', this circuit is from separately fine setting tap memory cell 62 (1) '-62 (N) ' extracts tap and selects the address.Every coarse adjustment delay line has relevant coarse adjustment tap able to programme to select circuit 64 (1) '-64 (N) ', this circuit is from separately coarse adjustment tap storage unit 66 (1) '-66 (N) ' extracts tap and selects the address.Tap selects circuit to change delay time according to tap position.
Press the emission mode run duration at impulsive synchronization device 22, provide signal to be continuously delivered to the input end of each treatment channel 17 (1)-17 (N) through storer 42 (see figure 4)s by microprocessor 38.The input signal of every treatment channel is converted into the sampled data sequence, propagates by fine setting tapped delay line 56 separately.In the demonstration structure of the impulsive synchronization device circuit that utilizes the charge-coupled image sensor delay line, the input signal of every treatment channel is converted into the charge packet sequence, propagates by fine setting and coarse adjustment tapped delay line subsequently.In the predetermined moment (this depends on the tap position that imaging system is selected constantly), whether the sampling of time-delay destroys information all is that selected tap is read from fine setting delay line 56.The sampling of time-delay is by the front end of the coarse adjustment delay line 58 of input correspondence successively.Then, selected time-delay sampling is propagated by the coarse adjustment delay line, and the information of whether destroying all reads from suitable tap position once more, and this tap position is corresponding to the predetermined delay time according to the operation assignment of the microprocessor 38 of ultrasonic image-forming system 10.Then, the sampled data that reads from the coarse adjustment delay line 58 (1)-58 (N) of every treatment channel is launched as ultrasonic pulsative signal by the transducer unit 18 (1)-18 (N) of correspondence through conversion.According to the preferred embodiment of the invention, the fine setting of each pulse synchronization circuit has different clock speeds with the coarse adjustment delay line.In emission mode, the wave beam that needs forms and the clock speed of focusing fine setting delay line both can be higher than the coarse adjustment delay line in order to finish, and can be lower than the coarse adjustment delay line again.
In another embodiment of the invention, produce the image that focuses in order to introduce suitable time-delay, form in circuit 26 and the pulse synchronization circuit 22 at wave beam and adopted adaptive beam to be formed into picture (ABI) technology.Adaptive beam forms technology and has improved picture quality and spatial resolution by containment by the artifact that scattering source and clutter cause in the sideband of transducer array response.This adaptive beam forms Circuits System and also can be configured on a slice chip.
It similarly is a kind of imaging reconstruction method based on model that derives from from the superresolution technology that adaptive beam is formed into.Adaptive beam forms imaging technique and is being improved aspect raising resolution, reduction sideband, clutter and the spot.For the improved superresolution algorithm of imaging comprises two dimension maximum probable method (MLM) and two-dimentional multiple signal classification method (MUSIC).Adaptive beam is formed into picture the backward scattering (amplitude and phase place) of needs is merged to come in, and has improved detection performance thereby compare with the conventional imaging method.
Figure 12 is a functional-block diagram, and it has described an embodiment that is arranged in the adaptive beam formation circuit 426 of scanner head 412 of the present invention.In adaptive beam forms circuit 426, in the finite impulse response filter independently the multiplier weighting controlled by backfeed loop, reduce clutter and interference or finite impulse response filter by this way.In two kinds of situations, adaptive circuit all is used to remove clutter and the interference that causes such as ultrasonic signal in the sideband of array of figure, so that the image of high-accuracy high-resolution to be provided.
Each treatment channel 428 (1)-428 (N) that wave beam forms circuit 426 receives from the signal of the gain control circuit 25 of change in time at separately tapped delay line 430.Wave beam forms circuit 426 and comprises N treatment channel 428, one of each transducer (passage) in the array 18.One group of weighting doubly takes advantage of D/A converter 432 to receive the signal that every tapped delay line is extracted out.Each treatment channel k comprises the multiplier 432 of M weighting, represents with 432k1-432kM.Set the power of multiplier 432, to produce output signal from every treatment channel, these output signals will be in summing junction 19 summations.Signal after the summation is sent to system, control circuit through system cable 416, as the microprocessor 438 in data processing and display unit 414.Microprocessor 438 analytic signals are determined every kind of known effect feature, as clutter, sideband and interference.Along with detection to this class effect, microprocessor 438 produces the control signal that is used to drive multiplier 432 weightings, and send this control signal to each multiplier through system cable 416 on circuit 440, this control signal is used for adjusting signal so that eliminate this class effect from output signal.Therefore, adaptive beam forms Circuits System and comprises feedback circuit, and this circuit changed the signal that receives from the tapped delay line of each passage before the signal summation.Read summing signal, and on the basis of reading, in backfeed loop, send the signal of proofreading and correct to multiplier to proofread and correct summing signal.Can compare by obtainable image with existing system, adaptive beam is formed into as the image that causes obtaining all much higher aspect resolution and picture quality.Adaptive beam forms imaging technique and causes resolution to increase substantially, and it is higher 2 to 3 times than the resolution that conventional imaging technique provides at least.As an example, be that the resolution that can obtain in the conventional ultrasonic system of 5MHz approximately is 1mm in frequency.Utilize adaptive beam to form imaging technique, the lateral resolution of acquisition is approximately 300 μ m.
Figure 13 is the detailed block scheme that wave beam of the present invention forms the circuit alternate embodiment, and this scheme replaces Fig. 6 and scheme shown in Figure 12.With reference to Figure 13, wave beam forms circuit 226 and can be used in dynamic beam formation and scanning in receiving mode.
As shown in figure 13.Wave beam forms circuit 226 and comprises N parallel treatment channel 217 (1)-217 (N), 18 1 passage (see figure 5)s in each unit in ultrasound transducer array.Each passage 217 (1)-217 (N) comprises delay unit 202 (1)-202 (N) separately, input sampling circuit able to programme 204 (1)-204 (N) separately, local storage separately and control circuit 206 (1)-206 (N), this circuit is used to sample circuit 204 (1)-204 (N) to store and produce reasonable time control, and stores and select suitable delay time for the view data sampling from sample circuit 204 (1)-204 (N) in delay circuit 202 (1)-202 (N).
Wave beam forms circuit 226 and also comprises central memory 203, the required whole delay value of treatment channel 217 (1)-217 (N) that this memory stores is all.In one embodiment, all the delay data value is downloaded storer and control circuit 206 (1)-206 (N) for every sweep trace central memory to all treatment channel 217 (1)-217 (N).Be stored in delay value in each local storage 206 (1)-206 (N) be used to control by each independently the sampling finished of sampling selecting circuit 204 (1)-204 (N) select, and control is subjected to each independently sampling time-delay of programmable delay unit 202 (1)-202 (N) influence.In a preferred embodiment, every image scanning line needs one group of special time-delay that is fit to all treatment channel, for example situation about forming at the phase shift array beams.In that embodiment, before carrying out every sweep trace, several groups of new delay values are downloaded to local storage 206 (1)-206 (N).Because the closeness of every delay line 202 (1)-202 (N), also because sample circuit 204 (1)-204 (N) corresponding with it and control circuit 206 (1)-206 (N) are simple, the wave beam formation Circuits System that this method allows to be used for 128 unit receiver array all is integrated in a slice chip.
Introduce the operation that wave beam forms circuit 226 now.At first in pre-amplification circuit 24 (1)-24 (N) and temporal gain control circuit 25 (1)-25 (N), amplify (see figure 5) by the echo of returning that transducer 18 (1)-18 (N) receives, send each self-corresponding sample circuit 204 (1)-204 (N) then to.Select the sample rate of this circuit 204 (1)-204 (N), fs makes it be higher than the clock speed of corresponding delay unit 202 (1)-202 (N), fc, promptly in a clock period of delay unit 202 (1)-202 (N), fs/fc possible sampling can be arranged.In the present invention, in this fs/fc possible sampling, select one, then it is loaded into delay unit 202 (1)-202 (N).Therefore, people will generally acknowledge, equably or anisotropically sampled data can choose and be loaded into delay unit 202 (1)-202 (N) from the echo of returning.
For example, if select sample rate than fast 8 times of time-delay clock speed, fs=8fc so, produces 8 sample data points at each delay line in the clock period.Select circuit 204 (1)-204 (N) to be used to from these 8 possible samplings, select one, then it is loaded into separately delay unit 202 (1)-202 (N).In addition, control circuit is integrated within each delay unit, so that maximum delay is that the programmable delay of M/fc is provided for the sampled data that each is loaded into delay unit, wherein M is the number of delay stages in the delay line of delay unit 202 (1)-202 (N), below in conjunction with Figure 15 introduction.
In each clock period of delay unit clock, be summed to together in summing circuit 219 from the output of every treatment channel 217 (1)-217 (N), so that the picture point of focusing to be provided.The summed data that is provided by summing circuit 219 is sent to A/D converter, and summed data is digitized there, so that send data processing and display device 14 to; Perhaps directly send summed data to data processing and display device 14 with the simulated data form.
Figure 14 A is the schematic block diagram of the exemplary embodiment of the sampling selecting circuit able to programme 204 of storer control among the present invention, the sequential of Figure 14 B explanation sampling process.In this example, suppose sample rate fs fast 8 times than the clock speed of delay time, promptly can be within the given clock period 1/fc of delay line 202 from 8 sampled data items of input waveform extracting.In this configuration, in time-delay clock period 1/fc, 8 equally spaced time control windows have been defined by sampling frequency fs.Under the control of storer and control circuit 206, in the cycle of each fc, during one of time control window, extract a sampling.
Storer and control circuit 206 comprise 3 BCD counters 216, and it is by the beat count of sampling frequency.Offer 3 to 8 demoders 220 as input from 3 output 218 of counter 216, this demoder one of 8 output lines 212 at it when enable state provide high level output, with the metric decoding numerical value of expression BCD input.8 to 1 MUX select a demoder output, so that select signal to offer sampling nmos pass transistor 214 sampling on the line 1126.
Be subjected to the control of three data outputs 228 of storer 210 by its selection wire by the selected line of MUX224.As shown in Figure 14B, if the storer output word is (0,0,0), select signal to provide a pulse by sampling on so online 226 at first sampling window.If memory word is (0,0,1), provide a pulse at second sampling window so, the rest may be inferred.The controlled stage of nmos pass transistor 214 (gate) selects signal to link to each other with sampling.Leak level (drain) and link to each other, and source class links to each other with delay line 202, so that the signal data sampling is provided with input waveform (echo of returning).
83 selection memory word is stored in addressable position in the storer 210.Among each cycle of delay line clock, the position in the storer 210 is to determine the address through address wire 232, so that 3 selected selection word of output on the sampling window as required online 228.Control circuit system 230 sampling window position on demand is set to suitable address with address wire.According to the address wire that is provided with, control circuit system 230 also will allow to send on the signal online 234 in each time-delay clock period, with permission demoder 220, MUX224 and storer 210 outputs, so that the sampling on online 1126 selects signal pulse to be positioned at suitable window.Because control circuit 230 can the selection memory address during each delay cycle, so can accurately control being uniform or uneven at interval or adopting the form of any needs between the sampling.
In one embodiment, control circuit 230 comprises their own inner memory circuits, and this circuit is preserved the sequence of addresses of control circuit 230 outputs, so that produce sampling pulse between reasonable time control window phase.This sequence of addresses was downloaded to this memory circuit from central memory 230 before carrying out every sweep trace.This memory circuit can be the storer as RAM and so on, also can be shift register.In any situation, memory circuit is all pressed beat required address of output data sampling between correct time control window phase of delay line clock.
Figure 15 is the detailed block scheme of the preferred replacement scheme of storer shown in Figure 14 A and control circuit 206A.This alternative form of storer and control circuit 206A comprises the memory circuit as shift register 205 and so on.In this embodiment, in the clock period of each delay unit 202, shift register 205 is all pressed 3 words storing in advance of speed fc displacement output of time-delay clock.Before carrying out every sweep trace, shift register 205 is stored in the register 205 at the output word of output line 209 superior displacements output.The time-delay that is used for sweep trace according to preparation is downloaded these words from central memory.In one embodiment, be stored in the number of words that is used for every sweep trace in the shift register 205 and equal focus number along every sweep trace.In the embodiment preferred, 512 focuses are arranged, therefore 512 3 words are arranged.In other words, shift register is one 512 grades 3 bit registers.
Storer and control circuit system 206A also comprise 3 BCD counters 207, and it is by selecting sample rate fs regularly.When the clock signal triggers it with the speed of fs, 3 BCD words of counter 207 outputs.In above-mentioned example, sample rate fs is 8 times of time-delay clock speed; So on output line 211, export 83 BCD words 0 for each word on the output line 209 of shift register 205 10To 7 10
All be sent to comparator circuit 213 from the output 209 of shift register 205 with from the output 211 of counter 207, this circuit relatively these two 3 words to determine whether they consistent.When their were consistent, comparator circuit 213 pointed out that both mates, exports a positive pulse on output line 1115.This pulse sends sampling nmos pass transistor 214 to, so that to returning echo sampling from suitable sound transducer 18.The simulated data that discrete time extracts is sent to corresponding suitable delay unit 202.
When from 3 BCD words of counter 207 with from 3 words couplings of shift register 205 time, positive pulse appears on output line 1115.Delay line clock speed fc is divided into 8 possible time control windows, and this will occur between one of them window phase.Therefore, the definite time of extracting the echo data that returns of 3 words that is stored in the shift register 205 is controlled window.So, in order to control time-delay, before carrying out concrete sweep trace, by downloading, 3 predetermined word schemes are stored among the shift register 205 from central memory 203.
Figure 16 is the detailed block scheme that Figure 13 wave beam extremely shown in Figure 15 forms the preferred embodiment of treatment channel 217 (1)-217 (N) in the circuit 226, the details of a preferred embodiment of its explanation programmable delay unit 202 (1)-202 (N).In this embodiment, each delay unit 202 (1)-202 (N) comprises M level charge-coupled image sensor programmable tap line 221 (1)-221 (N).Every grade provides an output, so for every delay line 221 (1)-221 (N) M parallel output is arranged.
In this embodiment, every delay line 221 (1)-221 (N) is had the control of the parallel digitized demoder 237 (1)-237 (N) of M output.According in the middle of selective M output, selecting one at decimal system numerical value from the decoding on the BCD incoming line of storer and control circuit 206.For example, 6 to 64 demoders 237 (1)-237 (N) can be used for providing output to select to 64 grades of charge-coupled image sensor delay lines 221 (1)-221 (N).At each time-delay clock period fc, by delay line 221 (1)-221 (N) time-delay, and on the selected output stage of demoder 237 (1)-237 (N), export from the discrete time analog sample of sampling selecting circuit 204 (1)-204 (N).The delay time that is loaded into each data sampling in the delay line can change continuously, so that dynamic focusing is provided.The data through sampling and time-delay from all passages 217 (1)-217 (N) are sued for peace in summing circuit 219.
In Figure 16, the incoming line 239 that leads to demoder 237 is from storer and control circuit 206.Figure 17 is the block scheme at length of the embodiment of storer and control circuit 206B, and this embodiment generates demoder incoming line 239.Except producing demoder incoming line signal 239, the circuit of Figure 17 is consistent with the circuit of Figure 15.In Figure 17, preferably select 512 grade of 9 parallel bit shift register 205A for use, its task is consistent with the register 205 among Figure 15, all is to produce 3 words on online 209, and these 3 words are used for comparator circuit 213 so that produce sampling pulse at the time of needs control window.Export 6 words simultaneously on best online 239, and it is sent to delay unit 202.As mentioned above, these 6 words are used as the input of above-mentioned demoder 237, so that select suitable level in tap charge-coupled image sensor delay line 221, sample of signal are introduced in suitable time-delay.
As storer in Figure 15 and control circuit 206A, the control word of sampling and time-delay downloaded to shift register 205A from central memory 203 before carrying out every sweep trace.Dispose at Figure 17 under the situation of 512 focuses, before carrying out every sweep trace, download 512 9 digitalized words.When determining the clock frequency of register 205A by delay unit clock speed fc, digitized 9 words online successively 239 and 209 outputs, next 9 words.The time control window that 3 word controls on online 209 are taken a sample from the echo of returning, and 6 word controls on online 239 are introduced the amount of delay of taking a sample by programmable delay for 202.
Figure 18 is the detailed block scheme of circuit modifications shown in Figure 17.The storer and the control circuit 206C that substitute among Figure 18 have reduced the volumes of storage space that needs in circuit 206.Adopt 512 grades of 2 words and need not 512 grades of 9 words.In this embodiment, no longer store the absolute delay time of the reality of each focus, but storage adjoin between the time-delay difference and (or) first second poor between differing from.In the occasion of storage second difference, only need two in order to store the delayed data that needs.Therefore, only need download 2 words, and store it by shift register 205B from central memory 203.In this case, 512 grades shift register only needs 2 bit wides.
Determine the clock frequency of register 205B again by time-delay clock fc.2 words output to integrating circuit 225 by register 205B, and this circuit can comprise the adder circuit of a twin-stage, are used for recovering actual time-delay from first and second differences of storage.The online 239A of integration step goes up and produces 6 words, and it is used as the control input of demoder 237 in the programmable delay unit 202.As mentioned above, online 209A goes up 3 additional bits that produce and uses in comparator circuit 213, so that produce sampling pulse at reasonable time control window.
Another embodiment of delayed processing circuit system is shown in Figure 19.Figure 19 is follow-on block scheme of Circuits System shown in Figure 13, and the output terminal in each programmable delay unit 202 (1)-202 (N) in this modified all comprises multiplier 250 (1)-250 (N).This configuration allows to adopt side lobe reduction, for example at receiving array by incorporating the Hamming weighting into, to reduce the sideband level and to produce better image quality.The weighted function of the multiplicand of each multiplier is to be provided by the memory buffer on the chip in storer and the control circuit 206 (1)-206 (N).The output of all multipliers 250 (1)-250 (N) is summed to form wave beam output at summing circuit 219.Be important to note that no matter still can both finish side lobe reduction at the input end of delay unit at the output terminal of delay unit 202 (1)-202 (N).Figure 20 represents a kind of time-delay structure of input end weighting.
In described all devices in conjunction with Figure 13 to Figure 20, minimum time-delay resolution is determined by sample rate fs.Figure 21 represents another kind of device, and the effective delay time ratio tc of this device is short.As what see in Figure 21, finite impulse response filter 252 (1)-252 (N) is added to the output terminal of delay circuit 202 (1)-202 (N).Finite impulse response filter 252 (1)-252 (N) can be used to produce the image sampling of time domain interpolation, and can be used to realize the time-delay resolution shorter than tc.For example, if the sampling that produces four interpolations by finite impulse response filter 252 (1)-252 (N), the resolution of delaying time so is tc/4.
Figure 22 comprise according to the finite impulse response (FIR) interpolation filter 252 of band fixed weighting multiplier 254 of the present invention-block scheme that individual exemplary embodiment is detailed.In general, multiplier needs two inputs, and the output of multiplier is the product of these two inputs.But multiplicand is fixed in fixed weighting multiplier 254, therefore only needs an input.Its output is to multiply by input with same multiplicand.
M level delay line 202 is used to preserve and the echo returned of conversion through sampling and time-delay.In each grade time-delay Q fixed weighting multiplier 254 of one cover arranged all, M * Q multiplier 254 promptly arranged.Therefore, as shown in figure 22, multiplier 254 can be counted as forming a two-dimensional array, and it has the capable and M row of Q.Each multiplier 254ij can use coordinate, and (wherein i is the row of multiplier for i, j) definition, and j is the delay stages of delay line 202, i.e. the row of array.
Just as seen in Figure 22, enjoy common input at the same multiplier that lists 254, this input is corresponding with one of input sampling.Enjoying common output with the multiplier in the delegation 254, this output is corresponding with one of sampling of passing through interpolation.Next, in each clock period Q sampling arranged.Sampling selecting circuit 256 can be placed on parallel delivery outlet, to select a sampling through interpolation, then it is sent to sum unit 219.
Figure 23 represents the schematic block diagram with another exemplary embodiment of the finite impulse response (FIR) interpolation filter 352 of multiplier 354 able to programme.M level delay line 202 is used to preserve and the echo returned of conversion through sampling and time-delay once more.In each grade time-delay multiplier 354k able to programme is arranged all, k=1 wherein, 2 ..., M.Just as seen in Figure 20, all multiplier 354k enjoy common output, and this output is corresponding with the sampling of the process interpolation of importing.Sampling through the time domain interpolation can produce on the basis of programming weighting.
As mentioned above, (r, θ) form receives ultrasonic signal and its digitizing to press the polar coordinates of the nature of ultrasonic signal.For demonstration, this expression mode is inconvenient, and (x, y) expression mode is for further processing again so it is transformed into rectangular coordinate.The rectangular coordinate representation is fit to the dynamic range and the brightness of various demonstrations and hard copy device through digitized correction.Data also can store and recover, so that show once more.When the conversion of doing between polar coordinates and the rectangular coordinate because (r, θ) point on the array with (x, y) point on the grid is inconsistent, so must be by point (r, θ) numerical evaluation point (x, numerical value y) at rectangular coordinate.
In the scan conversion system in early days, the visit (x, the y) point of each on the grid, and with simple linear interpolation by (r, the numerical evaluation of four points that θ) rely on recently on the array each (x, numerical value y).Finishing this task need use finte-state machine to produce transverse pattern, use bidirectional shift register in a large amount of Digital Logic and memory cell, to preserve (r, θ) data sampling is so that control computation process and guarantee the correct (r of asynchronous reception, θ) data sampling arrived to finish each (x, interpolation y) in the appropriate time.The early stage equipment of this class may be not only dumb but also be unnecessarily complicated.No matter control hardware is how expensive, may have only one by (x, y) path of array.This means and to obtain different ultrasonic scanning frequencies and whole advantages of imaging depth aspect.In other words, no matter physical reality, different data all are forced into same form.
In scanning conversion circuit 28 (see figure 4)s of the present invention, by using Digital Theory chart (number-theoretic scheme) to produce (x reliably by natural order, y) grid transverse path (grid traversal path), promptly getting (r, just utilize them when θ) taking a sample, thereby reduced the complicacy and the cost of hardware widely.This method provides greater flexibility and better fidelity for the medical data of reality, because its allows the transversal scanning (traversals) of array of designs, so that they do not expose the profile of factitious image repetition.This scanning conversion circuit 28 of the present invention adopts Farey-sequence generator method, and this method will generate (x, y) coordinate of each point according to the order that each point occurs in scanning process.
Suppose that system receives first pair of flying spot; Wish to differentiate all (x, y) whether integer is to dropping in 0＜y≤L interval.Introduce now and adopt the Farey sequence to produce that all (x, y) right method, this method make according to the order that angle increases progressively that (x is y) to dropping within two continuous arrays and satisfying 0＜y≤L.This method is utilized following true: some (x, y) to dropping on the same angle, so only produce that some are relatively prime (a, b) right, then according to (x, y)=n (a, b) be provided with remaining (x, y) right, n=1 wherein, 2 ..., till (n+1) b＞L.How to finish let us definition Farey sequence in order to understand this better.
Definition: denominator is no more than L and the sequence of the tactic rational number that increases progressively according to numerical value is called as the Farey sequence on L rank.
If U/V is the mark in the minterm, and V≤L, we will claim that U/V is L rank Farey marks.So the Farey mark is in the middle of minterm; Therefore its molecule and denominator are relatively prime.G.H.Hardy and E.M.Wright are once at " An Introduction tothe Teory of Number " (pp23-24, Oxford University Press, London, 1938) introduced the theory of Farey in, its content was incorporated into for your guidance at this.
With correlationship of the present invention be following relation.
Make a/b, c/d, e/f are three continuous L rank Farey marks, and
Z=[(L+b)/and d], wherein operator [] is to get greatest integer function (1)
So,
e＝Zc-a，f＝cd-b (2)
Formula 1 and 2 allows us to begin all remaining numerical value in the recursion interval from any two continuous Farey marks.
Figure 24 has illustrated a simple example, and this example utilizes 10 rank Farey marks to generate all (x, y) display dot in 46 radian to the 54 radian scopes on 10 * 10 grid.With the numerical value of first pair of continuous L rank Farey mark (L=10, a=1, b=1 and c=L-1=9, d=L=10) substitution formula 1 and 2 obtains next Farey mark, e=8, f=9.Utilize a=9 now, b=10 and c=8, d=9 repeat identical calculating, obtain next Farey mark, e=7, f=8 again.Obviously, always recursion go down just can produce given radian scope interior all (x, y) right.If the user wants to make same ray at one-tenth figure on the thinner show grid (for example wanting to become on the display dot 20 * 20 figure), we adopt same routine, but make L=20, promptly adopt 20 rank Farey marks to produce all (x, y) display dot.The simple algorithm explanation: (x, y)-to being (19,20), (18,19), (17,18) ...Just as seen in Figure 21, all net points within two continuous sweep traces all generate by the natural order that angle increases progressively, promptly
atan(10/9)＜atan(9/8)＜atan(8/7)＜atan(7/6)＜atan(6/5)＜atan(5/4)＜atan(9/7)＜atan(4/3)。This feature allows scan conversion system automatically to adapt to scanning angle φ 0Variation.Having at interval, the system of uneven scanning array able to programme can be equipped with Farey sequence device.In one embodiment of the invention, data processing and display unit 14 are programmed, and handle to carry out scan conversion.
As mentioned above, ultrasonic image-forming system 10 of the present invention also comprises continuous or pulse Doppler processor 36, and this processor allows to produce color flow cardon.Therefore, the target (the particularly blood of Liu Donging) that moves can be revealed, and the doctor need not be performed the operation just can see the situation of inside of human body.
The waveform 111 that belongs to together that is fit to the pulse Doppler ultrasonic imaging is expressed out in Figure 25.This waveform is made up of the train of impulses of N pulse, the degree of depth sampling that each pulse collection J is many like this in train of impulses.Figure 25 has also represented to be fit to the block scheme of the pulsed doppler signals processor 36 of this imaging technique, and wherein the echo of returning that each transducer receives before 113 place's homophases and quadrature demodulation is through sampling and summed., be stored in then in the memory buffer 119 through sampling with preserve circuit 115 and analog/digital converter converts data image signal to through the echo of demodulation, link up till all pulse echos of (coherentinterval) all arrive at interval until comprising.To from storer, read in N pulse echo of each degree of depth collection then. with control Doppler sideband, calculate the FFT (Farey fraction transformation) of N point with weighting sequence (v (n)) weighting then at 121 places.In this time, begin to handle from each degree of depth sampling that links up at interval by Doppler filter, arriving at and be stored in second memory buffer from the coherent echo at interval of the next one.But Dppler Integral Processing device described here is finished the repertoire that indicates in the frame of broken lines among Figure 25. except mould/transformation of variables, because equipment provides the analog sample data processing function, so the AD mapping function is unnecessary.Remaining circuit and operate in the United States Patent (USP) U.S.4 that is entitled as " Charge Domain parallel Processing Network ", 464, existing narration is incorporated its content for your guidance at this in 726 (the licensing to Alice M.Chiang on August 7th, 1984).The product of capable compute matrix of this pulse Doppler processor (PDP) device and matrix, so broad range of applicability.This device adopts and will organize the product that the way that the apposition that forms is sued for peace is calculated two real-valued matrixes (real valued matrix) with corresponding going of second matrix by first matrix column.For the application of pulse Doppler processor in doppler filtering is described, we at first include the doppler filtering equation in real-valued matrix summation.Doppler filtering is to finish by the discrete fourier transform (DFT) of the pulse echo of the weighting of calculating each interested degree of depth.If we usefulness g (wherein k is Doppler's index for k, j) the expression degree of depth-Doppler's sampling, and 0≤k≤N-1, j are depth factors, so have: g ( k , j ) = Σ n = 0 N - 1 v ( n ) f ( n , j ) exp ( - j 2 πkn / N ) - - - ( 3 )
Weighting function can combine with the kernel of an integral equation of DFT (discrete fourier transform) to obtain the matrix of Doppler filter conversion coefficient, and its matrix unit is provided by following formula:
w(k，n)＝w kn＝v(n)exp(-j2πkn/N) (4)
Real component and imaginary component through the signal of doppler filtering can be represented with following formula now: g r , kj = Σ n = 0 N - 1 ( W r , kn f r , nf - W i , kn f i , nj ) - - - ( 5 ) g r , kj = Σ n = 0 N - 1 ( W r , kn f i , nj - W i , kn f r , nj ) - - - ( 6 )
In equation 5 and 6, two indexes of two index variablees can be counted as matrix exponetial entirely.So Doppler filter can be expressed as the matrix product computing in matrix representation.People can see that the pulse Doppler processor can finish four multiplyings between the matrix, carry out the doppler filtering computing whereby.
DDP device 36 comprises J level charge-coupled image sensor tapped delay line 110, J charge-coupled image sensor multiplication and D/A converter (MDACs) 112, J * K totalizer 114, J * K Doppler sample buffer 517 and incorporates into and goes here and there out (parallel-in-serial-out) Output Shift Register 118 among the present invention.MDACs shares 8 public bit digital incoming lines, and the element of matrix of coefficients provides on this incoming line.The function that tapped delay line 110 is finished comprises sampling and preserves, the analog input signal that the time is continuous is transformed into analog sample.
Be in operation, the function of device 36 is as follows: with the real component of the echo returned or the input end that imaginary component imposes on tapped delay line 110.In the starting point of degree of depth window, be displaced to tapped delay line 110 with suitable speed abstract image sampling and with continuous degree of depth sampling.In case the degree of depth sampling from first pulse echo interval (PRT) is loaded, each element in first row of transform coefficient matrix W is sent successively to the public incoming line of MDACs112.The product that forms at each MDAC112 loads to sealing in and going out (serial-in-parallel-out) shift register 521.The set of the J * K of a Ji Suaning product in this way is equivalent to an outer product matrix.These products seal in and go out to be sent to each charge-coupled image sensor summation information source from each, and this information source will add up from the apposition element of each continuous PRI.Repeat this process till all pulse echos (have F capable) all dispose.
On this aspect, every group of k totalizer 114 preserved Doppler's sampling of k concrete degree of depth unit.The output that these Doppler sampling is sent to totalizer at synchronization is incorporated into and is gone here and there out shift register 519.These registers play the impact damper effect and preserve J * K Doppler's sampling, can begin immediately on the next one links up basis at interval so handle.At last, determining that totalizer shift register 521 is incorporated into to the output of device goes here and there out the beat of whole degree of depth sampling of the given unit of shift register 118 parallel transfers.In order to show flow graph, read each sampling with the order that suits the requirements from pulse Doppler processor device with serial mode.
Pulse Doppler processor-A the antetype device that is fit to 16 degree of depth samplings has created.Pulse Doppler processor-A is used to handle one group of echo waveform, and the sampling that is included in each pulse device collection in this group echo reaches 16.The ability of the running target a little less than the situation test micrometer that has strong DC clutter to exist is successfully confirmed by prototype pulse Doppler processor device.
In order to make the assembling device that the color flow cardon needs two pulse Doppler processors, as shown in figure 26 with ultrasonic image-forming system.In this device, handling a PRI interval, all w in top pulse Doppler processor elements 120 accounting equations 5 and 6 rf rAnd w if r, and following pulse Doppler processor elements 122 calculates all-w if iAnd w rf i.Then, the output of each component is sued for peace, so that alternately obtain g rAnd g i
As mentioned above, picture system of the present invention also comprises image compression circuit 34, and this circuit is adjusted data and its conversion is gone out compressed format, so that allow it is sent to a distant place.In preferred embodiments, the Image Data Compression circuit is United States Patent (USP) U.S.5,126,962 and U.S.5, the circuit of 030,953 described type, their exercise question are respectively " Discrete CosineTransform Processing System " and " Charge Domain Bloch MatchingProces-sing ", and, they are incorporated into for your guidance at this respectively on June 30th, 1992 and on July 9th, 1991 licensing to Alice M.Chiang.
Figure 27 is the block scheme of a preferred alternate embodiment of ultrasonic image-forming system of the present invention.In the embodiment of Figure 27, multiplier 319 is added among the scanner head 312 and between transducer array 318 and driver 20 and pre-amplification circuit 24.In this embodiment, all only handle signal at any given time from the part transducer array.For example, the array 318 of 128 transducers is arranged, in one embodiment, have only 64 unit to be handled simultaneously.Multiplier 319 is used to 64 signals are sent to pre-amplification circuit 24 and subsequent conditioning circuit.Multiplier 319 is gone back in the future, and the driving pulse of self-driven device 20 sends to current driven 64 unit in the array.This is called as in the embodiment of sub-hole scanning in the text, and the complicacy of circuit has been greatly simplified, because treatment channel only need offer several unit that has of handling, is 64 unit in this example.In this embodiment, image is by scanning transducer array 318 and activates unit that array adjoins selectively and transmit and receive ultrasonic signal and form.
In sub-hole scan period, picture quality may be because the intervention of picture noise descends, and this picture noise is to be caused by the image energy by sideband rather than the acquisition of dominant frequency band in the array response.In order to address this problem, in ARRAY PROCESSING, increased the spatial window wave filter to eliminate or to reduce energy from sideband.A kind of type of spatial window is the width that dynamically changes window according to the element number that is activated.Another kind is the constant window end to end of clipping.
Figure 28 is the curve of response of the spatial window of two types of explanations.In portable ultrasound system of the present invention, the design space window is for the sub-hole array element with maximum quantity is complementary, and spatial window does not change and dynamically changes along with the element number that is activated.The fundamental reason of this configuration is that utilization is dynamically opened (or emission) energy of spatial window minimizing reception not as good as utilizing the constant window end to end of clipping with regard to the image effect that obtains.For two kinds of situations, almost equal aspect minimizing picture noise.Therefore, it is favourable utilizing constant intercepting window, because its configuration is fairly simple and produce the quality better image.For example shown in Figure 28 (adopting Unit 64 sub-hole scanning and Blackman-Harris window), half (42%) of the energy that the too late constant intercepting window of energy that dynamic window provides when emission or reception provides.
Figure 29 A and 29B are the display mode synoptic diagram, and this mode can be used for display 32 of the present invention.The same a kind of demonstration display mode rather than the storage mode of providing with existing ultrasonic image-forming system, system of the present invention has multiple window display mode for user's selection.Figure 29 A represents selectable windows display device, wherein occurs three messagewindows on display simultaneously.The B-scan image of window A display standard, and window B shows the M-scan image of two-dimensional Doppler color flow cardon.Window C is the user profile window, and this window is notified user's select command and selected to provide convenience for the user is manual.The essential single window of Figure 29 B right and wrong shows.In this demonstration, complete display screen only provides a kind of B-scan image.Display can utilize screen to cut apart characteristic and make two width of cloth show overlapping or be arranged side by side and show B-mode scanning and two kinds of images of color Doppler scanning simultaneously.
Figure 30 A to Figure 30 D is with the relation between the used various transducer array configurations of schematic view illustrating the present invention and the corresponding image scanning district.Figure 30 A represents linear array 18A, and this array produces rectangular image scanning area 307A.This array generally includes 128 transducers.Introduce the time-delay of one group of definition figure image focus for every sweep trace.Because this array is linear and scanning area is a rectangle, the time-delay of every sweep trace is normally consistent.Therefore, only delay value need be downloaded to local storage and control circuit 206 (1) to 206 (N) from central memory 203 according to the present invention, a complete image only need be downloaded once.On the other hand, linear array 18A can be used as the phase shift array, every sweep trace is introduced the delay value of different controlling beams in this array.
Figure 30 B is with the relation between the transducer array 18B of schematic view illustrating bending and image scanning that obtain and local bending the district 307B.Array 18B still comprises 128 transducers that adjoin usually.The time-delay that every sweep trace is introduced can be consistent once more, perhaps changes time-delay in order to carry out phase shift array scanning process.
Relation between Figure 30 C explanation linear array 18C and the trapezoidal image area 307C.In this embodiment, array 18C is made up of 192 transducers that adjoin usually, rather than 128.By the linear sweep shown in Figure 30 A is combined with the phase shift array scanning, linear array is used to produce keystone scanning district 307C.In one embodiment, on the opposite end of array 8C, arrange 64 transducers, use, so that form the bent angle part at the two ends of regional 307C by phase shift array configuration.64 middle transducers use by linear scan pattern, so that realize the rectangle part of regional 307C.Therefore, trapezoid area 307C utilizes above-mentioned sub-hole scan method to realize in the method, having only 64 transducers at any time in action.In one embodiment, alternately be activated by 64 neighbour transducer group.In other words, at first be transducer 1-64 in action.Next, transducer 64-128 is activated.In next procedure, transducer 2-65 is activated, and then, transducer 65-129 is activated.Change continuously in such a way, till transducer 128-192 is activated.Again next, begin a new wheel scan from transducer 1-64 once more.
Figure 30 D explanation is finished the phase shift scanning imagery according to the present invention with the short array 18D of the linearity of transducer.Adopt linear array 18D through phase shift array beams diversion treatments, to produce the angle amplitude limit district 307D shown in Figure 30 D.
Figure 31 is according to circuit board function schematic block diagram of the present invention.It approximately is 2 inches * 4 inches multilayer circuit board that circuit board 1000 is preferably selected size.It preferably selects dual platen and utilizes the surface to paste embedding technique (surface-mount technology) to provide.The sort circuit system can be divided into radiating circuit 1010 and receiving circuit 1020 on function.Radiating circuit 1010 comprises pulse synchronization circuit 1022, this circuit and 1024 couplings of high-voltage drive/pulse-generator circuit.Driver/pulse producer 1024 is connected with multiplication module 1018 by emission/reception (T/R) switch 1016.
Pulse producer 1024 produces high-voltage pulse under the control of the delayed processing circuit system of pulse synchronization circuit 1022.These pulses are sent to transducer array 18 through T/R switch 1016 and multiplier 1018, to produce ultrasonic signal.Operation T/R switch 1016 does not influence responsive receiving circuit system 1020 with the high-voltage pulse that guarantees pulse producer 1024.It provides reverse-voltage protection with the diode protection structure to the preposition amplification time gain control circuit in the receiving circuit 1024.T/R switch 1016 is included in the electronic component of the insulation that sub-hole scan period uses, so as with no transducer unit with keep apart at the transducer unit of usefulness.This Circuits System also stops the phase mutual interference between the treatment channel that is caused by spur signal.
Receiving circuit 1020 comprises preposition amplification and temporal gain control circuit module 1022, Beam-former module 1026 and non-essential analogue-to-digital converters 1027.As shown in the figure, preposition amplification and two chip 1022-1 of temporal gain control circuit 1022 usefulness and 1022-2 represent.Every preposition amplification and temporal gain control chip are handled half bar at given time and are being used passage.The actual preposition amplification of using and the quantity of temporal gain control circuit 1022 chips are restricted by manufacturing process.It is best that preposition amplification and temporal gain control circuit 1022 are made into a slice chip.
Wave beam forms module 1026 can be included in the wave beam formation Circuits System of introducing in above-mentioned any embodiment.Module 1026 is preferably on a slice chip and forms, and comprises the requisite whole Circuits System of the above-mentioned wave beam formation function of realization.
The receiving circuit 1020 of radiating circuit 1010 and low pressure, every kind can be made into a slice chip.By the chip-count that reduces in the circuit, can reduce the size of circuit board 1000.Circuit board also is included in the discrete elements of mounted on surface, as resistance, capacitor, telefault etc., or their integrated equivalent.
Figure 32 is the diagrammatic cross-section of the linear sweep head of partly cut-away.Scanner head 1030 is closed among the plastic housing 1032.As shown in the figure, by support part 1034 circuit board 1000A is fixed within the housing 1032.Circuit board 1000A is connected with bus terminals device 1036, and this electric wire connecting junction is connected with the linear array 1038 of transducer by the flat cable or the printing flexible cable 1037 of softness.Concentric cable electric wire connecting junction 1035 makes scanner head 1030 and external electronic circuits coupling.Another kind of way is to adopt the electric wire connecting junction that is fit to twisted-pair cable.
Figure 33 is another sectional view of scanner head 1030 shown in Figure 32.As shown in the figure, support part 1034 is fixed two double-sided PCB 1000A and 1000B.Two or polylith circuit board can be single face also can be two-sided, and gathered into folds by one with suffering plot or dislocation so that maximally utilise free space, this depends on concrete application.These circuit boards separate by heat-conducting layer 1045, and this heat-conducting layer is as the heat radiator of Circuits System.Heat filling also can be filled within the housing.Support part 1034 preferably by the low-friction material such as teflon make with the insertion that helps circuit board 1000A and 1000B with extract.Every side of circuit board can preferably be processed 64 information channels from transducer 1038.So two double- sided PCB 1000A and 1000B can support 256 transducers as shown in the figure.
Figure 34 is the preferred embodiment of the transducer scanner head of bending, shows certain part with section.Scanner head 1040 is made of plastic housing 1042.Notice that handle portion can have outside rib gripping surface to be provided preferably and can optionally to be used to out louvre.Circuit board 1000A is fixing with teflon support part 1044.Circuit board is connected with bus terminals device 1046 with concentric cable 1035 (or twisted-pair cable).Bus terminals device 1046 links to each other with the curved arrays 1048 of transducer by printing flexible cable 1047.
Figure 35 is the synoptic diagram of insertable ultrasonic probe, shows certain part with section.This probe 1060 limits profile by housing 1062, and housing is divided into two parts: be fit to the elongated probe segment of insertion body cavity and the handle portion that suitable operator holds.Circuit board 1064 is fixed within probe 1060 the handle portion and with concentric cable 1065 and links to each other with transducer array 1068.Except be with the handle fit dimension smaller, circuit board 1064 is in full accord with the circuit board 1000 of Figure 30 on function.128 transducers (N=128) are preferably arranged in array 1068.In the sort of situation, it is sufficient for the operation probe that every face has the double-sided PCB 1064 of 64 treatment channel.
Figure 36 is a software block scheme of operating the ultrasonic device needs of narration here.Ultrasonic scanner 1072 and user's display 1078 has been described with figure.Signal processing module 1074 provides concrete hardware controls, and for example the signal processor of control figureization, custom chip and system are regularly.User's display 1078 is driven by user's graphic interface (GUI) 1076, for example Pi Pei those interfaces of band Windows.Virtual control panel 1075 provides the interface between user graphical interface 1076 and the hardware interface 1074.
Typical demonstration can utilize equipment to solidify frame data, prints frame data or the ability of frame data deposit is offered the user.The user can also emphasize color Doppler imaging area and Doppler's acoustic processing district.The user can also manually change the data that receive, for example depth of field.8 depth of field sections are preferably arranged.The user can also change the number (from 1 to 8) of the focal region of emission, changes the contrast and the brightness of image.
More particularly, the user can select imaging pattern.Provide B-pattern in order to adjust the demonstration of brightness or normal image.Flow (demonstration) as overlap mode or mode side by side in order to control color Doppler, C-is provided pattern.The doppler image that changes in time for the pattern control with independent imaging provides M-pattern.The sound doppler mode can be provided with and open or close, to replenish the demonstration of B-pattern and C-pattern.
The user can also determine transducer array, with the size and dimension of determining that image shows.Selection based on select for use actually curve pattern still be linear array still be the phase shift array.
The user can also import and show patient's data.So patient's data will be labeled in the demonstration.The computing machine that is used to provide image to show can be used software programming, so that show patient's case history and imaging data with window form.The various push-and-pull menus of mouse-based operation are provided to the user.
The user can also determine imaging pattern according to the concrete application of scanner.Or actually according to imaging for the diagnostic application of heart or stomach, for dept. of radiology use, or for obstetrics use, or for gynaecology uses, or peripheral vessel imaging applications, the user can automatically adjust the depth of field and the emissive power of image.The user can also manually adjust the depth of field of image and launch to satisfy client's application.
The transducer array that another embodiment preferred of the present invention relates in order to form two dimension has the capable supersonic imaging apparatus of two or more transducers that adjoin.Such just as the handheld device among Figure 37 600, the transducer portion 606 in the housing 600 comprises triplex row transducer 608,610 and 612.608,610 with 612 the row length can be different.For example, the length of 608 and 612 row can be shorter than 610 row of centre (be such as the length of centre row shorter line length 1.5 times).The interval of adjoining between the row both can be identical with the interval between the transducer in any given row, also can be greater than this at interval.Thicker line spacing can provide effective focusing for the ultrasonic signal that transducer array sends.The same with being connected in the above-mentioned embodiment, every capable transducer can be that circuit board is connected with chip carrier in the housing with one or more flexible cable.
Another preferred embodiment of the present invention relates to portable ultraphonic stethoscope system 700, and this system is shown in 38 figure.This system is incorporated in the synchronous and driver circuitry and the wave beam formation Circuits System of transducer array, array in the stethoscopic sound receptor housing (being the stethoscope head of front) 704.Stethoscopic receptor housing 704 links to each other with two earplugs 712, so that acoustic information is offered the user.Pipe core 705 is with housing 704 and Y type connecting pipe 707.Earplug 712 is installed on the pipe 706,708, and they extend out from Y-piece.Electric wire connecting junction (housing) 702 links to each other stethoscope with cable 710.Electric wire connecting junction (housing) 702 can make an integral body with Y-piece, or is installed on the Y-piece, or is assemblied on the housing 704.The transducer that is installed in the Y-piece 707 can be used to produce sound, and this sound is sent to earplug 712 along pipe 706,708.Stethoscope can be used to provide standard acoustic information, electro-acoustic information and (or) ultrasound information.
Wave beam in stethoscope receptor shell 704 forms the spatial image that Circuits System produces area-of-interest, and this image is sent to hand-held display 714 along cable 710, as individual digital display (personal digital assistant).The processor that comprises above-mentioned generation ultrasonoscopy in the display shell preferably selects for use the M-pattern to show or Doppler shows.The user can receive the voice data and the view data of area-of-interest simultaneously, and these data can be stored in storer, perhaps is sent to system separately by modulation along cable 720.Can provide power by the battery in the display shell 714, in the receptor shell 704 or the electric wire connecting junction shell.Housing 714 can comprise flat-panel monitor 716 (as LCD) and user interface 718 (as keyboard or mouse control).
Another preferred embodiment of the present invention is the ultrasonic system 800 shown in Figure 39 A and Figure 39 B.Transducer unit or array 802 usefulness adhesive plasters 805 are fixed on patient's the skin 810 in this embodiment.Adhesive plaster 805 can have bonded edge 806, so that adhesive plaster 805 is fixed on patient's the skin.Array 802 is received on the housing 804 that is worn on the health by cable 808 or wireless connections, this housing can record data and (or) with the position of data transmission to another receiver.The above-mentioned array 812 of a transducer unit or delegation or multirow can be arranged in the adhesive plaster shown in Figure 39 B 814.In should using, can also comprise on the adhesive plaster that wave beam forms and the focus circuit system.Can utilize the battery that is positioned at housing 804 power to be provided for transducer system and support circuit system.
Another embodiment preferred of the present invention relates to the promptly suitable conduit system of inserting body cavity of ultrasonic probe flexibly.This system 900 will be illustrated in conjunction with Figure 40 A and 40B.System 900 comprises flexible axle 902, and this has near-end 905 and the far-end 907 that is connected with shell 904.Above-mentioned treatment circuit is within shell 904.Shell 904 usefulness cables 910 link to each other with display 908 with user interface 906.The far-end 907 of probe axle comprises distal portions 912, and it is circuit board group component 916 that transducer array 918 and chip carrier are arranged among this part.Chip carrier 916 links to each other with cable 920, as what in application, introduced, this cable sends control signal to impulsive synchronization device, drive circuit and wave beam forms and focus circuit, and sends the electrical image through summation of area-of-interest in the shell 904 treatment circuit system.The outer wall 922 of axle seals, so that inner components and parts and working environment are completely cut off.Transducer array can be by radial directed, promptly can be along the conduit axis in distal orientation.Can optionally comprise cavity 914, use for optical fiber observing system, lead or other processing or surgical apparatus.
The present invention has done elaboration particularly with reference to embodiment preferred when, the people who is familiar with this technology is to be understood that the present invention in form and details can make various variations, but these variations all do not break away from the spirit and scope of the present invention that claims are determined.

Claims (40)

1. ultrasonic image-forming system comprises:
Ultrasonic transducer device, this device receive from the ultrasonic signal of area-of-interest reflection and will receive ultrasonic signal be transformed into electric signal;
Treatment circuit system, this system receive electric signal and produce the electrical image of area-of-interest;
Housing, ultrasonic transducer device and treatment circuit system are all in this housing; And
Interface transmits electrical image by this interface.
2. ultrasonic image-forming system according to claim 1, wherein treatment circuit comprises that wave beam forms Circuits System, this system comprises:
Be fit to the programmable sampling selecting circuit of transducer devices, described sampling selecting circuit is being controlled the sampling of electric signal, so that extracts electric signal at one of numerous time control windows that set in advance; And
The delay circuit that is fit to each transducer, this circuit make the electric signal time-delay of being extracted by sampling selecting circuit, so that these electric signal can be used to produce the electrical image of area-of-interest.
3. ultrasonic image-forming system according to claim 1, this system further comprises the battery-powered portable flat panel display equipment that links to each other with interface.
4. ultrasonic image-forming system according to claim 2, wherein delay circuit comprises charge-coupled image sensor programmable tap delay line.
5. ultrasonic image-forming system according to claim 2, the electric signal that wherein is extracted are the analog sample of discrete time.
6. ultrasonic image-forming system according to claim 1, this system further comprises the pulse synchronization circuit system, the signal that this synchro system will be controlled the time offers ultrasound transducer array, so that the control ultrasonic transducer is to the time of region of interest emission ultrasonic signal.
7. ultrasonic image-forming system according to claim 1, this system further comprises amplification system, this Circuits System is amplified the electric signal from the ultrasonic transducer device.
8. ultrasonic image-forming system according to claim 1, this system further comprises driver circuitry, this Circuits System produces the signal that drives the ultrasonic transducer device so that launch ultrasonic signal.
9. ultrasonic image-forming system according to claim 2, this system further comprises the memory circuitry system, this Circuits System is used to store the data that are fit to control wave beam formation Circuits System.
10. ultrasonic image-forming system according to claim 1, this system further comprises the gain control circuit system, this control system control is from the level of the electric signal of ultrasonic transducer device.
11. ultrasonic image-forming system according to claim 1, wherein the ultrasonic transducer device comprises the linear array of ultrasonic transducer.
12. ultrasonic image-forming system according to claim 1, wherein area-of-interest is interested trapezoid area.
13. ultrasonic image-forming system according to claim 1, wherein the ultrasonic transducer device is the curve pattern of ultrasonic transducer.
14. ultrasonic image-forming system according to claim 1, wherein the ultrasonic transducer device is the phase shift array of ultrasonic transducer.
15. ultrasonic image-forming system according to claim 2, sampling selecting circuit wherein able to programme comprises memory circuit, sequence of values of this memory circuitry stores, sampling selecting circuit able to programme will be used this sequence of values to be controlled at time control window and extract electric signal.
16. ultrasonic image-forming system according to claim 15, wherein memory circuit is the shift register that walks abreast.
17. ultrasonic image-forming system according to claim 15, sampling selecting circuit wherein able to programme further comprises:
Counter, this counter are exported a series of BCD words; And
Comparator circuit, this circuit compare each BCD word and the numerical value of storing with control and extract the electric signal sampling in memory circuit.
18. ultrasonic image-forming system according to claim 1, this system comprises further and is fit to form the storer that Circuits System is downloaded delay value to wave beam that described delay value will be used to make the electric signal time-delay from ultrasonic transducer.
19. a scanner head that is used for ultrasonic image-forming system, this scanner head comprises:
Ultrasound transducer array, this array received is from the ultrasonic signal of area-of-interest reflection, and transducer is transformed into electric signal with the ultrasonic signal of receiving;
Wave beam forms Circuits System, and this Circuits System receives electric signal, and described wave beam forms Circuits System and comprises:
The sampling selecting circuit able to programme that is fit to each transducer, the extraction of described sampling selecting circuit control sampling, so that control one of windows in the numerous times that set in advance and extract electric signal; And
The delay circuit that is fit to each transducer, this circuit make the electric signal time-delay of extracting from sampling selecting circuit, so that these electric signal can be used to produce the electrical image of area-of-interest;
Housing, built-in ultrasonic transducer and wave beam form Circuits System in this housing; And
Interface is sent to treatment circuit system with electrical image from housing by this interface.
20. scanner head according to claim 19, wherein delay circuit comprises charge-coupled image sensor programmable tap delay line.
21. scanner head according to claim 19, the electric signal that wherein is extracted are the analog sample of discrete time.
22. scanner head according to claim 19, this scanner head further comprises the pulse synchronization circuit system, the signal that this synchro system will be controlled the time offers ultrasound transducer array, so that the control ultrasonic transducer is to the time of region of interest emission ultrasonic signal.
23. scanner head according to claim 19, this scanner head further comprises amplification system, and this Circuits System is amplified the electric signal from ultrasonic transducer.
24. scanner head according to claim 19, this scanner head further comprises driver circuitry, and this Circuits System produces the signal that drives ultrasonic transducer so that launch ultrasonic signal.
25. scanner head according to claim 19, this scanner head further comprises the memory circuitry system, and this Circuits System is used to store the data that the control wave beam forms Circuits System.
26. scanner head according to claim 19, this scanner head further comprises the gain control circuit system, and this control system control is from the level of the electric signal of ultrasonic transducer device.
27. scanner head according to claim 19, wherein ultrasound transducer array is a linear array.
28. scanner head according to claim 27, wherein area-of-interest is interested trapezoid area.
29. scanner head according to claim 19, wherein ultrasound transducer array is a curve pattern.
30. scanner head according to claim 19, wherein ultrasound transducer array is the phase shift array.
31. scanner head according to claim 19, this scanner head further comprises storer, and this storer is fit to delay value is downloaded to wave beam formation Circuits System, and described delay value is used to make the electric signal time-delay from ultrasonic transducer.
32. the method with ultrasonic energy scanning area-of-interest, this method comprises:
The ultrasonic transducer device is provided;
Receive from the ultrasonic signal of area-of-interest reflection with the ultrasonic transducer device, and the ultrasonic signal of receiving is transformed into electric signal by the ultrasonic transducer device;
The treatment circuit system is provided, and this system receives electric signal and produces the electrical image of area-of-interest; And
Provide interface, so that electrical image is sent to housing separately.
33. method according to claim 32, this method further comprises:
Form Circuits System with wave beam and extract the electric signal sampling, so that each electric signal sampling all is extracted at one of numerous times control windows that set in advance, and make the sampling time-delay that is extracted, so that utilize electric signal to form electrical image through sampling and time-delay.
34. the step that provides wave beam to form Circuits System further is provided for method according to claim 32, this method, this Circuits System comprises the charge-coupled image sensor programmable tap delay line that is fit to each transducer, so that the electric signal that is extracted time-delay.
35. method according to claim 33, the electric signal that wherein is extracted are the analog sample of discrete time.
36. method according to claim 32, this method further comprises the step that the pulse synchronization circuit system is provided, this synchro system offers ultrasonic transducer with time control signal, so that the control ultrasonic transducer is to the time of region of interest emission ultrasonic signal.
37. method according to claim 32, this method further comprises:
To amplify from the electric signal of ultrasound transducer array; And
Make electric signal and wave beam form the Circuits System coupling through amplifying.
38. method according to claim 32, this method further are included in, and storage is used to control the data that wave beam forms Circuits System in the storer, described storer downloads data to forming the relevant local storage of circuit with wave beam.
39. method according to claim 32, this method further comprise with the level of gain control circuit system control from the electric signal of ultrasonic transducer device.
40. method according to claim 32, this method further comprises the image that produces area-of-interest.
CN96195104A 1995-06-29 1996-06-28 Portable ultrasound imaging system Pending CN1189217A (en)

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