CN105581812B - Automatic adjustment method and system for ultrasonic imaging equipment - Google Patents
Automatic adjustment method and system for ultrasonic imaging equipment Download PDFInfo
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Abstract
The invention provides an automatic adjustment method and system of ultrasonic imaging equipment, wherein the method comprises the following steps: s1, adjusting a scanning state according to any one of the initial focal position, the initial transmitting frequency, the initial receiving frequency and the initial receiving bandwidth in the current depth state of the image; s2, selecting a plurality of local sampling areas at equal intervals under the current depth of the image; s3, judging whether each local sampling area belongs to an organization signal or a noise signal according to the pixel point coordinates in each local sampling area; s4, acquiring the attribute value of the image; the attribute values are: the number of tissue signals/(the number of tissue signals + the number of noise signals), or the number of noise signals/(the number of tissue signals + the number of noise signals) S5, determining whether to change the current scanning state according to the attribute value; the invention improves the convenience and the use efficiency of the clinical diagnosis of the ultrasonic imaging equipment.
Description
Technical field
The invention belongs to ultrasonic diagnostic imaging field, it is related to a kind of Automatic adjustment method for supersonic imaging apparatus and is
System.
Background technology
Ultrasonic imaging becomes clinic because of many advantages such as its non-invasive, real-time, easy to operate, cheap
On one of the diagnostic tool that is most widely used.
Especially during ultrasonic scan, it is necessary first to which the initial parameter state of supersonic imaging apparatus, the parameter are set
State determines quality, the precision of scanning image.
On existing supersonic imaging apparatus, the user usually needs to adjust the focus position under each picture depth state manually
It sets, the parameters such as tranmitting frequency, receives frequency and reception bandwidth, the precision adjusted manually can not ensure, for Clinical practice
Efficiency has a significant impact.
Invention content
The purpose of the present invention is to provide a kind of Automatic adjustment method of supersonic imaging apparatus and systems.
One of in order to achieve the above-mentioned object of the invention, the automatic adjustment side of the supersonic imaging apparatus of an embodiment of the present invention
Method, the method includes：
S1, under the current depth state of image, according to specified any initial focus position, initial transmissions frequency, just
Beginning receives frequency and initial reception bandwidth adjust scanning state；
S2, multiple local sampling regions are equidistantly chosen under the current depth of described image；
S3, judge that each local sampling region belongs to tissue signal according to the pixel point coordinates in each local sampling region
Or noise signal；
S4, the attribute value for obtaining image, the attribute value are：
The quantity of tissue signal/(quantity of quantity+noise signal of tissue signal),
Or the quantity of noise signal/(quantity of quantity+noise signal of tissue signal)；
S5, it is confirmed whether to change current scanning state according to the attribute value；
It is swept if the attribute value between the first system attribute thresholds and second system attribute thresholds, keeps current
Look into state；
If the attribute value is more than or equal to the first system attribute thresholds, or is less than or equal to second system attribute thresholds, then sentence
Whether the focal position of breaking is most shallow position or most deep position under current depth state；The first system attribute thresholds are big
In the second system attribute thresholds；
If so, after adjusting the tranmitting frequency, receives frequency and reception bandwidth, return to step S3；
If it is not, after then adjusting the focal position in the depth direction, step S3 is returned to.
As being further improved for an embodiment of the present invention, the step S3 is specifically included：
The mean variance of all pixels in each local sampling region is obtained according to the focal position；
According to the mean variance in each local sampling region confirm each local sampling region belong to tissue signal or
Noise signal；
If the mean variance is less than systematic variance mean value threshold value, judge that the local sampling region is noise signal；
If the mean variance is more than or equal to systematic variance mean value threshold value, judge that the local sampling region is believed for tissue
Number.
As being further improved for an embodiment of the present invention, the step S3 is specifically included：
To the pixel in each local sampling region along X, Y both direction using in gradient operator removal signal message
Essential information retains the profile information in the noise information and signal message in each local sampling region, and will obtain figure
As being indicated with gray level image 1；
Each gray level image is filtered to the gray level image 1 in each local sampling region into line trace using connected graph method
Profile information in 1 retains the noise information in each gray level image 1, and obtained image is indicated with gray level image 2；
According to each local sampling area of corresponding with its gray level image in each local sampling region of each original image 2
Domain obtains the variance in each local sampling region；
If the variance is less than systematic variance threshold value, judge that the local sampling region is noise signal；
If the variance is more than or equal to systematic variance threshold value, judge that the local sampling region is tissue signal.
As being further improved for an embodiment of the present invention, " adjusts the tranmitting frequency in the step S5, receives frequency
Rate and reception bandwidth " specifically includes：
The adjustment factor of fixed value is respectively configured for tranmitting frequency, receives frequency, reception bandwidth, each adjustment factor takes
Value is ranging between 0 to 1；
If under current depth state, the local sampling region quantity for belonging to tissue signal is more than the part for belonging to noise signal
Sampling area quantity, then by the tranmitting frequency, receives frequency, reception bandwidth difference divided by respective adjustment factor；
If under current depth state, the local sampling region quantity for belonging to tissue signal is less than the part for belonging to noise signal
The tranmitting frequency, receives frequency, reception bandwidth are then multiplied by respective adjustment factor by sampling area quantity respectively.
As being further improved for an embodiment of the present invention, the step S1 is specifically included：
It is corresponding to choose multiple focal positions, tranmitting frequency, receives frequency and reception under multiple depth states of image
Bandwidth；
The corresponding focal position of multiple images depth, tranmitting frequency, receives frequency and reception bandwidth are passed through into sample
The fit approach of curve or batten broken line generates respective curve matching figure；
Under the current depth state of image, the first of corresponding current depth state is obtained by searching for the curve matching figure
Beginning focal position, initial transmissions frequency, initial receives frequency and initial reception bandwidth；
Under the current depth state of image, according to the initial focus position, initial transmissions frequency, initial receives frequency
And initial reception bandwidth adjusts scanning state.
One of in order to achieve the above-mentioned object of the invention, the automatic adjustment system of the supersonic imaging apparatus of an embodiment of the present invention
System, the system comprises：Module is adjusted, is used under the current depth state of image, according to specified any initial focus position
It sets, initial transmissions frequency, initial receives frequency and initial reception bandwidth adjust scanning state；
Processing module, for equidistantly choosing multiple local sampling regions under the current depth of described image；
According to the pixel point coordinates in each local sampling region judge each local sampling region belong to tissue signal or
It is noise signal；
The attribute value of image is obtained, the attribute value is：
The quantity of tissue signal/(quantity of quantity+noise signal of tissue signal),
Or the quantity of noise signal/(quantity of quantity+noise signal of tissue signal)；
It is confirmed whether to change current scanning state according to the attribute value；
It is swept if the attribute value between the first system attribute thresholds and second system attribute thresholds, keeps current
Look into state；
If the attribute value is more than or equal to the first system attribute thresholds, or is less than or equal to second system attribute thresholds, then sentence
Whether the focal position of breaking is most shallow position or most deep position under current depth state；The first system attribute thresholds are big
In the second system attribute thresholds；
If so, after adjusting the tranmitting frequency, receives frequency and reception bandwidth, again to described image at
Reason, until the attribute value is between the first system attribute thresholds and second system attribute thresholds；
If it is not, after then adjusting the focal position in the depth direction, described image is handled again, until described
Attribute value is between the first system attribute thresholds and second system attribute thresholds.
As being further improved for an embodiment of the present invention, the processing module is specifically used for：
The mean variance of all pixels in each local sampling region is obtained according to the focal position；
According to the mean variance in each local sampling region confirm each local sampling region belong to tissue signal or
Noise signal；
If the mean variance is less than systematic variance mean value threshold value, judge that the local sampling region is noise signal；
If the mean variance is more than or equal to systematic variance mean value threshold value, judge that the local sampling region is believed for tissue
Number.
As being further improved for an embodiment of the present invention, the processing module is specifically used for：
To the pixel in each local sampling region along X, Y both direction using in gradient operator removal signal message
Essential information retains the profile information in the noise information and signal message in each local sampling region, and will obtain figure
As being indicated with gray level image 1；
Each gray level image is filtered to the gray level image 1 in each local sampling region into line trace using connected graph method
Profile information in 1 retains the noise information in each gray level image 1, and obtained image is indicated with gray level image 2；
According to each local sampling area of corresponding with its gray level image in each local sampling region of each original image 2
Domain obtains the variance in each local sampling region；
If the variance is less than systematic variance threshold value, judge that the local sampling region is noise signal；
If the variance is more than or equal to systematic variance threshold value, judge that the local sampling region is tissue signal.
As being further improved for an embodiment of the present invention, the processing module is specifically used for：
The adjustment factor of fixed value is respectively configured for tranmitting frequency, receives frequency, reception bandwidth, each adjustment factor takes
Value is ranging between 0 to 1；
If under current depth state, the local sampling region quantity for belonging to tissue signal is more than the part for belonging to noise signal
Sampling area quantity, then by the tranmitting frequency, receives frequency, reception bandwidth difference divided by respective adjustment factor；
If under current depth state, the local sampling region quantity for belonging to tissue signal is less than the part for belonging to noise signal
The tranmitting frequency, receives frequency, reception bandwidth are then multiplied by respective adjustment factor by sampling area quantity respectively.
As being further improved for an embodiment of the present invention, the adjustment module is specifically used for：
It is corresponding to choose multiple focal positions, tranmitting frequency, receives frequency and reception under multiple depth states of image
Bandwidth；
The corresponding focal position of multiple images depth, tranmitting frequency, receives frequency and reception bandwidth are passed through into sample
The fit approach of curve or batten broken line generates respective curve matching figure；
Under the current depth state of image, the first of corresponding current depth state is obtained by searching for the curve matching figure
Beginning focal position, initial transmissions frequency, initial receives frequency and initial reception bandwidth；
Under the current depth state of image, according to the initial focus position, initial transmissions frequency, initial receives frequency
And initial reception bandwidth adjusts scanning state.
Compared with prior art, the beneficial effects of the invention are as follows：The Automatic adjustment method of the supersonic imaging apparatus of the present invention
And system, according to the current location of image, automatically adjust the focal position of supersonic imaging apparatus, tranmitting frequency, receives frequency with
And width is received, improve the convenience and service efficiency of the clinical diagnosis of supersonic imaging apparatus.
Description of the drawings
Fig. 1 is the flow signal for the Automatic adjustment method for supersonic imaging apparatus that an embodiment of the present invention provides
Figure；
Fig. 2 is the flow diagram of the one of which realization method of step S1 in Fig. 1；
Fig. 3 is the flow diagram of the one of which realization method of step S3 in Fig. 1；
Fig. 4 is the flow diagram of the one of which realization method of step S3 in Fig. 1；
Fig. 5 is the flow diagram of the one of which realization method of step S5 in Fig. 1；
Fig. 6 is the data relationship table of comparisons with N group parameters in a specific example of the invention；
Fig. 7 A, 7B, 7C, 7D are the ultrasound parameter curve matching figure in a specific example of the invention；
Fig. 8 is the division schematic diagram in local sampling region in a specific example of the invention；
Fig. 9 is the module signal for the automatic regulating system for supersonic imaging apparatus that an embodiment of the present invention provides
Figure.
Specific implementation mode
Below with reference to embodiment shown in the drawings, the present invention will be described in detail.But embodiment is not intended to limit this
Invention, structure that those skilled in the art are made according to these embodiments, method or transformation functionally are wrapped
Containing within the scope of the present invention.
As shown in Figure 1, the Automatic adjustment method for supersonic imaging apparatus that Fig. 1 an embodiment of the present invention provides, institute
The method of stating includes：
S1, under the current depth state of image, according to specified any initial focus position, initial transmissions frequency, just
Beginning receives frequency and initial reception bandwidth adjust scanning state.
For the convenience of description, in an of the invention specific example, initial focus position is indicated with P0, initial transmissions frequency with
TF0 indicates that initial receives frequency indicates that initial reception bandwidth is indicated with W0 with RF0, in the embodiment, initial focus position,
Initial transmissions frequency, initial receives frequency and initial reception bandwidth are arbitrarily designated, and can be corresponded between parameters,
It can also not correspond to mutually.
In conjunction with shown in Fig. 2, in a preferred embodiment of the invention, one group of initial position is obtained using a rough algorithm
Parameter value, to reduce subsequent regulating step, the parameter value includes focal position, tranmitting frequency, receives frequency and connects
Take-up is wide.
In the preferred embodiment, the method specifically includes following steps：
P1, under multiple depth states of image, it is corresponding choose multiple focal positions, tranmitting frequency, receives frequency and
Reception bandwidth.
In present embodiment, under each depth state of figure, the focal position, tranmitting frequency, receives frequency and
Reception bandwidth is unique parameter value.
The one-to-one parameter value of the group can obtain multigroup one-to-one ginseng by manual adjusting in the prior art
Number, can also be obtained by the empirical value of user and preserve multigroup one-to-one parameter.
Such as：In conjunction with shown in Fig. 6, the data relationship table of comparisons with N group parameters is established, wherein Depth indicates figure
As depth, Focus indicates that focal position, TFreq indicate that tranmitting frequency, RFreq indicate that receives frequency, RBW indicate reception bandwidth.
Wherein, D1, D2, D3 ... D (N) represent different picture depths, and P1, P2, P3 ... P (N) represent above-mentioned different images
Focal position under depth, TF1, TF2, TF3 ... TF (N) represent the tranmitting frequency under above-mentioned different images depth, RF1, RF2,
RF3 ... RF (N) represent the reception centre frequency under above-mentioned different images depth, and W1, W2, W3 ... W (N) represent above-mentioned different images
Reception signal bandwidth under depth, N are the natural number more than or equal to 1.
In an embodiment of the present invention, the parameter value that one group of initial position is obtained using rough algorithm further includes following step
Suddenly：
P2, the corresponding focal position of multiple images depth, tranmitting frequency, receives frequency and reception bandwidth are passed through
The fit approach of spline curve or batten broken line generates respective curve matching figure.
In conjunction with shown in Fig. 7 A-7D, in specific example of the invention, multiple curves are generated using the fit approach of batten broken line
Fitted figure, the curve matching figure include：Under identical image depth, the curve matching figure of focal position, the curve of tranmitting frequency
The curve matching figure of fitted figure, the curve matching figure of receives frequency, reception bandwidth.
P3, under the current depth state of image, obtain corresponding current depth state by searching for the curve matching figure
Initial focus position, initial transmissions frequency, initial receives frequency and initial reception bandwidth.
In present embodiment, one group of parameter can be obtained by way of taking a little, such as：First determine current picture depth,
Later respectively on different curve matching figures, picture depth is searched according to abscissa, and carried out on multiple curve matching figures
Mark, ordinate can intuitively show the relevant parameter of unique one group of initial position of corresponding present image depth, including：It is burnt
Point position, initial transmissions frequency, initial receives frequency and initial reception bandwidth.
P4, under the current depth state of image, according to the initial focus position, initial transmissions frequency is initial to receive
Frequency and initial reception bandwidth adjust scanning state.
According to the above-mentioned initial parameter obtained using rough method, the current scanning depth state of correspondence image is specified just
Beginning focal position, initial transmissions frequency, initial receives frequency and initial reception bandwidth, and adjust scanning state by it；
In conjunction with shown in Fig. 8, in an embodiment of the present invention, the Automatic adjustment method for supersonic imaging apparatus is also wrapped
It includes：
S2, multiple local sampling regions are equidistantly chosen under the current depth of described image；
In present embodiment, in order to which equipment is adjusted to optimal location, it is generally the case that local sampling region need to cover whole
A depth bounds.Preferably, each local sampling region is equal in magnitude, and spacing is equal.
It is understood that the quantity in the local sampling region is not specifically limited, when its quantity is more, equipment
Adjusting position is more accurate, and certainly, the quantity in local sampling region increases, and also can accordingly increase computation complexity.
In the preferred embodiment of the present invention, the quantity value range in the local sampling region is [picture depth (unit
Mm)/1mm, 4* picture depth (unit mm)/1mm].
S3, judge that each local sampling region belongs to tissue signal according to the pixel point coordinates in each local sampling region
Or noise signal.
In the specific implementation mode of the present invention, step S3 is realized using two ways.
In conjunction with shown in Fig. 3, in a kind of embodiment, the step S3 is specifically included：
M1, the mean variance that all pixels in each local sampling region are obtained according to the focal position；
In a specific example of the invention, the mean variance is obtained using following formula.
Wherein, MSE indicates that the mean variance of all pixels in each local sampling region, a are the nature more than or equal to 1
Number, m indicate that the pixel number in local sampling region, n are to participate in meter in current local sampling region when calculating pixel variance
The pixel number of calculation, the n≤m, (i, j) indicate that any of which pixel in local sampling region, p, q are combined with each other
Afterwards, indicate with current (i, j) as basic point, in local sampling region to the left, to the right, upwards, move down after any pixel point.
It should be noted that when calculating the mean variance in each local sampling region, the value all same of m, n.
In the preferred embodiment of the present invention, local sampling region can choose square area, in order to calculate.
Such as：Pixel number m=9*9=81 in local sampling region chooses and participates in calculating in current local sampling region
Pixel number n=3*3=9, be not described in detail herein.
M2, confirmed according to the mean variance in each local sampling region each local sampling region belong to tissue signal or
It is noise signal；
If the mean variance is less than systematic variance mean value threshold value, judge that the local sampling region is noise signal；
If the mean variance is more than or equal to systematic variance mean value threshold value, judge that the local sampling region is believed for tissue
Number.
In the specific embodiment of the invention, the systematic variance mean value threshold value is systemic presupposition value, can be according to user
Demand, current image attributes etc. are arbitrarily adjusted, and are not described in detail herein.
In conjunction with shown in Fig. 4, in another embodiment of the present invention, the step S3 is specifically included：
N1, signal message is removed using gradient operator along X, Y both direction to the pixel in each local sampling region
In essential information, retain the profile information in the noise information and signal message in each local sampling region, and will
It is indicated to image with gray level image 1；
In specific example of the present invention, original image μx(m, n) can obtain gray level image in N1 steps by two ways
1。
In a kind of embodiment, first to original image μx(m, n) is handled in X direction, is carried out later along Y-direction to it
Processing；In another embodiment, first to original image μx(m, n) is handled along Y-direction, later to it along Z-direction
Reason；The gray level image 1 that above two mode obtains is identical.
It is illustrated and is introduced with one such embodiment.
In the example, first to original image μx(m, n) is handled in X direction；
Processing procedure is as follows：μx(m, n)=μ (m+1, n)-μ (m, n)；
It is handled along Y-direction later；μxy(m, n)=μx(m, n+1)-μx(m, n)
μxy(m, n) indicates gray level image 1.
N2, each gray scale is filtered to the gray level image 1 in each local sampling region into line trace using connected graph method
Profile information in image 1 retains the noise information in each gray level image 1, and by obtained image with 2 table of gray level image
Show.
Under normal conditions, continuous lines in each gray level image 1 are defined as profile information.
Gray level image 2 is indicated with v (m, n) in a specific example of the invention.
N3, it is adopted according to each part of corresponding with its gray level image in each local sampling region of each original image 2
Sample region obtains the variance in each local sampling region；
If the variance is less than systematic variance threshold value, judge that the local sampling region is noise signal；
If the variance is more than or equal to systematic variance threshold value, judge that the local sampling region is tissue signal.
In specific example of the present invention, the variance is obtained using following formula,
Wherein, variance indicates that the variance of all pixels in each local sampling region, (m, n) indicate local sampling area
Any of which pixel in domain.
In the specific embodiment of the invention, the systematic variance threshold value be systemic presupposition value, can according to user demand,
Current image attributes etc. is arbitrarily adjusted, and is not described in detail herein.
In an embodiment of the present invention, the Automatic adjustment method for supersonic imaging apparatus further includes：
S4, the attribute value for obtaining image, the attribute value are：
The quantity of tissue signal/(quantity of quantity+noise signal of tissue signal),
Or the quantity of noise signal/(quantity of quantity+noise signal of tissue signal)；
In specific example of the present invention, the quantity of tissue signal is indicated with I, and the quantity of noise signal is indicated with K, then each to adopt
The attribute value in sample region is：I/ (I+K) or K/ (I+K).
In the preferred embodiment for the present invention, the attribute value is weighed with amount of noise K/ (I+K).
Further, in an embodiment of the present invention, the Automatic adjustment method for supersonic imaging apparatus further includes：
S5, it is confirmed whether to change current scanning state according to the attribute value；
It is swept if the attribute value between the first system attribute thresholds and second system attribute thresholds, keeps current
Look into state；The first system attribute thresholds are more than the second system attribute thresholds；
If the attribute value is more than or equal to the first system attribute thresholds, or is less than or equal to second system attribute thresholds, then sentence
Whether the focal position of breaking is most shallow position or most deep position under current depth state；
If so, after adjusting the tranmitting frequency, receives frequency and reception bandwidth, return to step S3；
If it is not, after then adjusting the focal position in the depth direction, step S3 is returned to.
It should be noted that the first system attribute thresholds of present embodiment, second system attribute thresholds are also system
Preset value can arbitrarily be adjusted according to the scanning performance etc. of user demand, equipment, is not described in detail herein.
According to the characteristic of ultrasonic scan equipment, it is generally the case that if the attribute value is more than or equal to the first system attribute threshold
Value, then using current location as basic point, adjust downwards focal position；If the attribute value is less than or equal to second system attribute thresholds,
Then using current location as basic point, it is adjusted up focal position；In this example, it is extremely current that it is corresponding, which to be adjusted up focal position,
Most shallow position under depth state, the corresponding extreme most deep position under current depth state of downward adjusting position.
In the embodiment of the invention, such as：Specified the first system attribute thresholds are 1/3, second system attribute
Threshold value is 1/20, and the quantity in local sampling region is 16.
Using current focal position, tranmitting frequency, receives frequency, reception bandwidth as initial position, by above-mentioned step
The attribute value obtained after rapid then confirms to be currently best scanning position, progress is set again without between 1/3 and 1/20
It adjusts；If the attribute value is more than or equal to 1/3 or is less than or equal to 1/20, if the attribute value is more than or equal to 1/3, with present bit
It is set to basic point, adjusts focal position downwards；If the attribute value is less than or equal to 1/20, using current location as basic point, to up-regulation
Save focal position.
The step of above-mentioned adjustment tranmitting frequency, receives frequency and reception bandwidth, specifically includes：For tranmitting frequency, connect
The adjustment factor of fixed value is respectively configured in receipts frequency, reception bandwidth, and the value range of each adjustment factor is between 0 to 1；
If under current depth state, the local sampling region quantity for belonging to tissue signal is more than the part for belonging to noise signal
Sampling area quantity, then by the tranmitting frequency, receives frequency, reception bandwidth difference divided by respective adjustment factor；
If under current depth state, the local sampling region quantity for belonging to tissue signal is less than the part for belonging to noise signal
The tranmitting frequency, receives frequency, reception bandwidth are then multiplied by respective adjustment factor by sampling area quantity respectively.
In a specific example of the invention, such as the adjustment factor of corresponding tranmitting frequency, receives frequency, reception bandwidth is distinguished
For：C1、C2、C3.
It is described in the preferred embodiment for the present invention, C1=C2=C3, certainly, and in the other embodiment of the present invention, institute
The value for stating C1, C2, C3 can be any number between 0 to 1, not be described in detail herein.
Then above-mentioned adjustment process is represented by：
New TF0=C1 x TF0, New RF0=C2 x RF0, New W0=C3 x W0；
Or New TF0=TF0/C1, New RF0=RF0/C2, New W0=W0/C3.
Further, repeat the above steps S3, S5, and the corresponding optimum position of current depth, i.e., the described category are arrived until adjusting
Property value is not described in detail herein between the first system attribute thresholds and second system attribute thresholds.
In conjunction with shown in Fig. 9, in an embodiment of the present invention, the automatic regulating system for supersonic imaging apparatus includes：It adjusts
Mould preparation block 100, processing module 200.
It adjusts module 100 to be used under the current depth state of image, according to specified any initial focus position, initially
Tranmitting frequency, initial receives frequency and initial reception bandwidth adjust scanning state.
In a preferred embodiment of the invention, adjustment module 100 is additionally operable to obtain at the beginning of one group using a rough algorithm
The parameter value of beginning position, to reduce subsequent regulating step, the parameter value includes focal position, tranmitting frequency, receives frequency
And reception bandwidth.
In this example, adjustment module 100 is specifically used for：It is corresponding to choose multiple focuses under multiple depth states of image
Position, tranmitting frequency, receives frequency and reception bandwidth；By the corresponding focal position of multiple images depth, tranmitting frequency,
Receives frequency and reception bandwidth generate respective curve matching figure by the fit approach of spline curve or batten broken line；Scheming
Under the current depth state of picture, by searching for the curve matching figure obtain corresponding current depth state initial focus position,
Initial transmissions frequency, initial receives frequency and initial reception bandwidth；Under the current depth state of image, according to described initial
Focal position, initial transmissions frequency, initial receives frequency and initial reception bandwidth adjust scanning state.
In conjunction with shown in Fig. 8, processing module 200 is used for：Multiple parts are equidistantly chosen under the current depth of described image to adopt
Sample region；According to the pixel point coordinates in each local sampling region judge each local sampling region belong to tissue signal or
Noise signal；The attribute value of image is obtained, the attribute value is：The quantity of the tissue signal/(quantity of tissue signal+noise letter
Number quantity) or noise signal quantity/(quantity of quantity+noise signal of tissue signal)；Confirmed according to the attribute value
Whether current scanning state is changed；
It is swept if the attribute value between the first system attribute thresholds and second system attribute thresholds, keeps current
Look into state；The first system attribute thresholds are more than the second system attribute thresholds；
If the attribute value is more than or equal to the first system attribute thresholds, or is less than or equal to second system attribute thresholds, then sentence
Whether the focal position of breaking is most shallow position or most deep position under current depth state；If so, adjusting the transmitting
After frequency, receives frequency and reception bandwidth, described image is handled again, until the attribute value is between the first system
Between attribute thresholds and second system attribute thresholds；If it is not, after then adjusting the focal position in the depth direction, again to institute
It states image to be handled, until the attribute value is between the first system attribute thresholds and second system attribute thresholds.
Processing module 200 specifically judges that each local sampling region belongs to tissue signal or noise letter using two ways
Number.In one way in which, processing module 200 is specifically used for：It is obtained in each local sampling region according to the focal position
The mean variance of all pixels；Confirm that each local sampling region belongs to group according to the mean variance in each local sampling region
Knit signal or noise signal；If the mean variance is less than systematic variance mean value threshold value, judge that the local sampling region is
Noise signal；If the mean variance is more than or equal to systematic variance mean value threshold value, judge that the local sampling region is believed for tissue
Number.
Wherein in another way, processing module 200 is specifically used for：To the pixel in each local sampling region along X,
Y both directions retain the noise letter in each local sampling region using the essential information in gradient operator removal signal message
Profile information in breath and signal message, and image will be obtained and indicated with gray level image 1；Using connected graph method, to each office
Gray level image 1 in portion's sampling area filters the profile information in each gray level image 1, retains each gray-scale map into line trace
As the noise information in 1, and obtained image is indicated with gray level image 2；According to each local sampling of each original image
Each local sampling region of corresponding with its gray level image in region 2 obtains the variance in each local sampling region；If the side
Difference is less than systematic variance threshold value, then judges that the local sampling region is noise signal；If the variance is more than or equal to systematic variance
Threshold value then judges that the local sampling region is tissue signal.
This hair is invented in an embodiment, when adjusting the tranmitting frequency, receives frequency and reception bandwidth, processing module
200 are specifically used for that the adjustment factor of fixed value, each adjustment factor are respectively configured for tranmitting frequency, receives frequency, reception bandwidth
Value range be between 0 to 1；If under current depth state, the local sampling region quantity for belonging to tissue signal is more than
Belong to the local sampling region quantity of noise signal, then it is the tranmitting frequency, receives frequency, reception bandwidth is respectively divided by respective
Adjustment factor；If under current depth state, belong to tissue signal local sampling region quantity be less than belong to noise signal
The tranmitting frequency, receives frequency, reception bandwidth are then multiplied by respective adjustment factor by local sampling region quantity respectively.
It should be noted that those skilled in the art in the invention can be understood that, for description convenience and
Succinctly, in the system of foregoing description module specific work process and specific example, preceding method embodiment can be referred to
In corresponding process and specific example, details are not described herein.
In conclusion the Automatic adjustment method and system of the supersonic imaging apparatus of the present invention, according to the current location of image,
Focal position, tranmitting frequency, receives frequency and the reception for automatically adjusting supersonic imaging apparatus are wide, improve supersonic imaging apparatus
Clinical diagnosis convenience and service efficiency.
For convenience of description, it is divided into various modules when description apparatus above with function to describe respectively.Certainly, implementing this
The function of each module is realized can in the same or multiple software and or hardware when application.
As seen through the above description of the embodiments, those skilled in the art can be understood that the application can
It is realized by the mode of software plus required general hardware platform.Based on this understanding, the technical solution essence of the application
On in other words the part that contributes to existing technology can be expressed in the form of software products, the computer software product
It can be stored in and preserve in medium, such as ROM/RAM, magnetic disc, CD, including some instructions are used so that a computer equipment
(can be personal computer, Information Push Server either network equipment etc.) executes each embodiment of the application or reality
Apply the method described in certain parts of mode.
Device embodiments described above are only schematical, wherein the module illustrated as separating component
It may or may not be physically separated, the component shown as module may or may not be physics mould
Block, you can be located at a place, or may be distributed on multiple network modules.It can be selected according to the actual needs
In some or all of module realize the purpose of present embodiment scheme.Those of ordinary skill in the art are not paying creation
Property labour in the case of, you can to understand and implement.
The application can be used in numerous general or special purpose computing system environments or configuration.Such as：Personal computer, information
Push server computer, handheld device or portable device, multi-processing module system, are based on microprocessor mould at laptop device
The system of block, set top box, programmable consumer-elcetronics devices, network PC, minicomputer, mainframe computer including to take up an official post
The distributed computing environment etc. of what system or equipment.
The application can describe in the general context of computer-executable instructions executed by a computer, such as program
Module.Usually, program module includes routines performing specific tasks or implementing specific abstract data types, program, object, group
Part, data structure etc..The application can also be put into practice in a distributed computing environment, in these distributed computing environments, by
Task is executed by the connected remote processing devices of communication network.In a distributed computing environment, program module can be with
It is preserved in medium positioned at the local and remote computer including preserving equipment.
It should be appreciated that although this specification is described in terms of embodiments, but not each embodiment only includes one
A independent technical solution, this description of the specification is merely for the sake of clarity, and those skilled in the art should will say
As a whole, the technical solution in each embodiment may also be suitably combined to form those skilled in the art can for bright book
With the other embodiment of understanding.
The series of detailed descriptions listed above only for the present invention feasible embodiment specifically
Bright, they are all without departing from equivalent implementations made by technical spirit of the present invention not to limit the scope of the invention
Or change should all be included in the protection scope of the present invention.
Claims (10)
1. a kind of Automatic adjustment method for supersonic imaging apparatus, which is characterized in that the method includes：
S1, under the current depth state of image, according to specified any initial focus position, initial transmissions frequency initially connects
It receives frequency and initial reception bandwidth adjusts scanning state；
S2, multiple local sampling regions are equidistantly chosen under the current depth of described image；
S3, judged according to the pixel point coordinates in each local sampling region each local sampling region belong to tissue signal or
Noise signal；
S4, the attribute value for obtaining image, the attribute value are：
The quantity of tissue signal/(quantity of quantity+noise signal of tissue signal),
Or the quantity of noise signal/（The quantity of quantity+noise signal of tissue signal）；
S5, it is confirmed whether to change current scanning state according to the attribute value；
If the attribute value between the first system attribute thresholds and second system attribute thresholds, keeps current scanning shape
State；
If the attribute value is more than or equal to the first system attribute thresholds, or is less than or equal to second system attribute thresholds, then institute is judged
State whether focal position is most shallow position or most deep position under current depth state；The first system attribute thresholds are more than institute
State second system attribute thresholds；
If so, after adjustment tranmitting frequency, receives frequency and reception bandwidth, return to step S3；
If it is not, after then adjusting focal position in the depth direction, step S3 is returned to.
2. the Automatic adjustment method according to claim 1 for supersonic imaging apparatus, which is characterized in that the step S3
It specifically includes：
The mean variance of all pixels in each local sampling region is obtained according to focal position；
Confirm that each local sampling region belongs to tissue signal or noise according to the mean variance in each local sampling region
Signal；
If the mean variance is less than systematic variance mean value threshold value, judge that the local sampling region is noise signal；
If the mean variance is more than or equal to systematic variance mean value threshold value, judge that the local sampling region is tissue signal.
3. the Automatic adjustment method according to claim 1 for supersonic imaging apparatus, which is characterized in that the step S3
It specifically includes：
To the pixel in each local sampling region along X, Y both direction using basic in gradient operator removal signal message
Information retains the profile information in the noise information and signal message in each local sampling region, and will obtain image with
Gray level image 1 indicates；
It is filtered in each gray level image 1 to the gray level image 1 in each local sampling region into line trace using connected graph method
Profile information, retain the noise information in each gray level image 1, and obtained image is indicated with gray level image 2；
It is obtained according to each local sampling region of corresponding with its gray level image in each local sampling region of each original image 2
Take the variance in each local sampling region；
If the variance is less than systematic variance threshold value, judge that the local sampling region is noise signal；
If the variance is more than or equal to systematic variance threshold value, judge that the local sampling region is tissue signal.
4. the Automatic adjustment method according to claim 1 for supersonic imaging apparatus, which is characterized in that the step S5
In " adjustment tranmitting frequency, receives frequency and reception bandwidth " specifically include：
The adjustment factor of fixed value, the value model of each adjustment factor are respectively configured for tranmitting frequency, receives frequency, reception bandwidth
It encloses between 0 to 1；
If under current depth state, the local sampling region quantity for belonging to tissue signal is more than the local sampling for belonging to noise signal
Region quantity, then by the tranmitting frequency, receives frequency, reception bandwidth difference divided by respective adjustment factor；
If under current depth state, the local sampling region quantity for belonging to tissue signal is less than the local sampling for belonging to noise signal
The tranmitting frequency, receives frequency, reception bandwidth are then multiplied by respective adjustment factor by region quantity respectively.
5. the Automatic adjustment method according to any one of claims 1 to 4 for supersonic imaging apparatus, which is characterized in that
The step S1 is specifically included：
It is corresponding to choose multiple focal positions, tranmitting frequency, receives frequency and receive band under multiple depth states of image
It is wide；
The corresponding focal position of multiple images depth, tranmitting frequency, receives frequency and reception bandwidth are passed through into batten song
The fit approach of line or batten broken line generates respective curve matching figure；
Under the current depth state of image, the initial coke of corresponding current depth state is obtained by searching for the curve matching figure
Point position, initial transmissions frequency, initial receives frequency and initial reception bandwidth；
Under the current depth state of image, according to the initial focus position, initial transmissions frequency, initial receives frequency and
Initial reception bandwidth adjusts scanning state.
6. a kind of automatic regulating system for supersonic imaging apparatus, which is characterized in that the system comprises：
Module is adjusted, under the current depth state of image, according to specified any initial focus position, initial transmissions to be frequently
Rate, initial receives frequency and initial reception bandwidth adjust scanning state；
Processing module, for equidistantly choosing multiple local sampling regions under the current depth of described image；
Belong to tissue signal according to each local sampling region of pixel point coordinates judgement in each local sampling region or makes an uproar
Acoustical signal；
The attribute value of image is obtained, the attribute value is：
The quantity of tissue signal/(quantity of quantity+noise signal of tissue signal),
Or the quantity of noise signal/（The quantity of quantity+noise signal of tissue signal）；
It is confirmed whether to change current scanning state according to the attribute value；
If the attribute value between the first system attribute thresholds and second system attribute thresholds, keeps current scanning shape
State；
If the attribute value is more than or equal to the first system attribute thresholds, or is less than or equal to second system attribute thresholds, then institute is judged
State whether focal position is most shallow position or most deep position under current depth state；The first system attribute thresholds are more than institute
State second system attribute thresholds；
If so, after adjustment tranmitting frequency, receives frequency and reception bandwidth, described image is handled again, until
The attribute value is between the first system attribute thresholds and second system attribute thresholds；
If it is not, after then adjusting focal position in the depth direction, described image is handled again, until the attribute value is situated between
Between the first system attribute thresholds and second system attribute thresholds.
7. the automatic regulating system according to claim 6 for supersonic imaging apparatus, which is characterized in that the processing mould
Block is specifically used for：
The mean variance of all pixels in each local sampling region is obtained according to focal position；
Confirm that each local sampling region belongs to tissue signal or noise according to the mean variance in each local sampling region
Signal；
If the mean variance is less than systematic variance mean value threshold value, judge that the local sampling region is noise signal；
If the mean variance is more than or equal to systematic variance mean value threshold value, judge that the local sampling region is tissue signal.
8. the automatic regulating system according to claim 6 for supersonic imaging apparatus, which is characterized in that the processing mould
Block is specifically used for：
To the pixel in each local sampling region along X, Y both direction using basic in gradient operator removal signal message
Information retains the profile information in the noise information and signal message in each local sampling region, and will obtain image with
Gray level image 1 indicates；
It is filtered in each gray level image 1 to the gray level image 1 in each local sampling region into line trace using connected graph method
Profile information, retain the noise information in each gray level image 1, and obtained image is indicated with gray level image 2；
It is obtained according to each local sampling region of corresponding with its gray level image in each local sampling region of each original image 2
Take the variance in each local sampling region；
If the variance is less than systematic variance threshold value, judge that the local sampling region is noise signal；
If the variance is more than or equal to systematic variance threshold value, judge that the local sampling region is tissue signal.
9. the automatic regulating system according to claim 6 for supersonic imaging apparatus, which is characterized in that the processing mould
Block is specifically used for：
The adjustment factor of fixed value, the value model of each adjustment factor are respectively configured for tranmitting frequency, receives frequency, reception bandwidth
It encloses between 0 to 1；
If under current depth state, the local sampling region quantity for belonging to tissue signal is more than the local sampling for belonging to noise signal
Region quantity, then by the tranmitting frequency, receives frequency, reception bandwidth difference divided by respective adjustment factor；
If under current depth state, the local sampling region quantity for belonging to tissue signal is less than the local sampling for belonging to noise signal
The tranmitting frequency, receives frequency, reception bandwidth are then multiplied by respective adjustment factor by region quantity respectively.
10. being used for the automatic regulating system of supersonic imaging apparatus according to claim 6 to 9 any one of them, which is characterized in that
The adjustment module is specifically used for：
It is corresponding to choose multiple focal positions, tranmitting frequency, receives frequency and receive band under multiple depth states of image
It is wide；
The corresponding focal position of multiple images depth, tranmitting frequency, receives frequency and reception bandwidth are passed through into batten song
The fit approach of line or batten broken line generates respective curve matching figure；
Under the current depth state of image, the initial coke of corresponding current depth state is obtained by searching for the curve matching figure
Point position, initial transmissions frequency, initial receives frequency and initial reception bandwidth；
Under the current depth state of image, according to the initial focus position, initial transmissions frequency, initial receives frequency and
Initial reception bandwidth adjusts scanning state.
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| CN108209966B (en) * | 2017-12-29 | 2021-02-12 | 深圳开立生物医疗科技股份有限公司 | Parameter adjusting method and device of ultrasonic imaging equipment |
| CN110930465B (en) * | 2019-11-29 | 2023-07-28 | 京东方科技集团股份有限公司 | Ultrasonic imaging method and equipment |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1799511A (en) * | 2005-01-03 | 2006-07-12 | 美国西门子医疗解决公司 | Ultrasonic imaging system |
| CN101879076A (en) * | 2009-05-08 | 2010-11-10 | 深圳迈瑞生物医疗电子股份有限公司 | Method and device for automatically optimizing Doppler ultrasonic imaging |
| CN101972152A (en) * | 2010-12-01 | 2011-02-16 | 深圳市蓝韵实业有限公司 | Method for automatically optimizing gain parameter of B-type image |
| CN101987023A (en) * | 2009-07-31 | 2011-03-23 | 深圳迈瑞生物医疗电子股份有限公司 | Gain compensation and image optimization method and device for ultrasonic imaging and system |
| CN103110432A (en) * | 2011-11-16 | 2013-05-22 | 美国西门子医疗解决公司 | Adaptive image optimization in induced wave ultrasound imaging |
| CN103356242A (en) * | 2012-03-29 | 2013-10-23 | 深圳市蓝韵实业有限公司 | Pulse repetition frequency adjustment method and high pulse Doppler imaging device |
| CN103845077A (en) * | 2012-12-05 | 2014-06-11 | 深圳迈瑞生物医疗电子股份有限公司 | Gain optimization method for ultrasound images and ultrasound imaging gain automatic optimization device |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US9084576B2 (en) * | 2012-07-13 | 2015-07-21 | Siemens Medical Solutions Usa, Inc. | Automatic doppler gate positioning in spectral doppler ultrasound imaging |
-
2015
- 2015-12-08 CN CN201510897552.1A patent/CN105581812B/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1799511A (en) * | 2005-01-03 | 2006-07-12 | 美国西门子医疗解决公司 | Ultrasonic imaging system |
| CN101879076A (en) * | 2009-05-08 | 2010-11-10 | 深圳迈瑞生物医疗电子股份有限公司 | Method and device for automatically optimizing Doppler ultrasonic imaging |
| CN101987023A (en) * | 2009-07-31 | 2011-03-23 | 深圳迈瑞生物医疗电子股份有限公司 | Gain compensation and image optimization method and device for ultrasonic imaging and system |
| CN101972152A (en) * | 2010-12-01 | 2011-02-16 | 深圳市蓝韵实业有限公司 | Method for automatically optimizing gain parameter of B-type image |
| CN103110432A (en) * | 2011-11-16 | 2013-05-22 | 美国西门子医疗解决公司 | Adaptive image optimization in induced wave ultrasound imaging |
| CN103356242A (en) * | 2012-03-29 | 2013-10-23 | 深圳市蓝韵实业有限公司 | Pulse repetition frequency adjustment method and high pulse Doppler imaging device |
| CN103845077A (en) * | 2012-12-05 | 2014-06-11 | 深圳迈瑞生物医疗电子股份有限公司 | Gain optimization method for ultrasound images and ultrasound imaging gain automatic optimization device |
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