DE69728343T2 - Method and device for image processing - Google Patents

Description

The The present invention relates to a method and a method Image processing device with the ability to display the image Information of multiple tomographic images in the depth direction.

Under The ultrasound examination device sends the imaging examination devices an ultrasonic wave in an examination body receives echoed back ultrasonic waves of bodies with different acoustic impedances, processed the ultrasonic received signals to a tomographic image and generates the image for examination of the examination body Presentation.

The MRI device uses the phenomenon the nuclear magnetic resonance for measuring the density distribution of Nuclear spins, the relaxation time distribution, etc. for the region of interest test article and generates from the measured data a tomographic image of the Investigation body.

The CT radiation device implements the radioactive irradiation through the entire surface the examination body, detects the radiation and assembles the detected signals for generating a (single) image of a tomographic image.

The various above mentioned Imaging equipment is sometimes for illustration designed a three-dimensional image, and the simplest Scheme for it is known the IP (intensity projection) Method is.

These Allow facilities the three-dimensional observation of blood vessels, the spatial relationship between the injury or lesion and the blood vessels as well the assessment of size and nature of a tumor, on the basis of a series of projected ones Images that are generated by, for example, the viewing angle (Viewpoint) changes in small steps.

The mentioned above IP method is to create a projected image (IP image) by extraction of the greatest value (or the smallest value or a specific value) from the Pixels from all tomographic images of the object.

For example, in the case of the ultrasonic inspection device, the image data of multiple (frames of images) generated by means of a movement of the ultrasonic probe, as in 1 As shown, a particular value is extracted from the pixels along all lines of sight, producing a frame of the projected image.

For extracting a certain value, the method uses a comparator as in 2A to compare the value of the pixel in the depth direction sequentially along a line of sight. The method of so-called Power Doppler Imaging, which extracts the largest value as a Doppler Power projection value, represents the relationship of the Doppler power value) relative to the depth of the imaging, as in FIG 2 B is shown.

The IP method with respect to the largest value is called the MIP (maximum intensity projection) Method referred to, the IP method with respect to the smallest Value is referred to as the MinIP (Minimum Intensity Projection) method, and The IP method with respect to a specific value is called the IP method with special value called.

In in the case of the ultrasonic imaging device, for example the MIP procedure with regard to the greatest value effective for Extract the blood vessel wall as well as from HV tissue, for example, from a tumor with a relatively large Brightness, and the MinIP method with reference to the smallest value is effective to extracting one tubular or vascularized tissue, such as a blood vessel and a Bile duct.

At the Extracting a part, for example a blood vessel, based on the projection process running the MinIP procedure, that a blood vessel with a low Brightness brings to the display. If, however, in another picture There is a pixel along the same line of sight that is darker than the blood vessel, will extracts the darker pixel instead of the blood vessel. Because of that The IP method involves such a problem that it is difficult is, blood vessels clear to show.

One Another problem is that in the extraction of a lighter part of a bloodstream as a power doubling image, especially when the viewer is watching blood vessels Intended to run in the depth direction, the IP method is not can represent which of the lighter illustrated intersect Blood vessels on the Front is located. This means, it is so far insufficient that the position information compressed in the depth direction and completely lost in the projection goes.

This fact is in the 3A . 3B and 3C shown in which the more hatched part of the lighter part and the weaker hatched part represents the darker part in the display or in the representation. If 3A and 3B Show blood vessels that run in front or behind, the above-mentioned MIP process creates a projected image as shown in FIG 3C and fails to reveal the positional relationship of the intersecting blood vessels in the depth direction.

A similar situation is in the 4A . 4B and 4C in which the more hatched part represents the brighter part and the weaker hatched part represents the darker part in the illustration. By doing 4A and 4B Show blood vessels that run in front or behind, the above-mentioned MIP process generates a projected image, as shown in 4C is shown and erroneously represents the intersecting blood vessels as if the lighter blood vessel were behind on the front instead.

Similar Problems also arise with the CT imaging as well as with the MR Imaging. A CT image of transverse organs, to Example of bronchi, as well as a CT image and an MRI image based on transverse blood vessels on a contrast medium, for example, fail in their spatial Reveal relation in the depth direction.

in the Document WO-A-9530914 is for the generation of high-resolution Pictures show the post-processing of angiographic images, for example, by a Magnetic Resonance Imaging (MRI) system or a computerized axial tomography (CAT) system were. The system contains preferably a data collection device for generating a data record, a Computer processor that interfaces with the data collection device owns and is set up the record for a projection to take a picture of the object while projecting it Create record, and an extraction device with a Interface to a computer that is responsible for receiving the projected Data record for the extraction of image properties adapted from it, by putting the projected record at least with thresholds provides two predetermined values.

post-processing techniques generate high-resolution and useful clinical pictures that are particularly suitable for the Investigation of diseases and inadequacies in which the body and are of particular use for magnetic resonance angiography or for applications, where a liquid flow in the Body monitors must become.

As a result, It is an object of the present invention to provide a method as well a device for image processing with the ability to specify in short Time a tomographic image with information in the depth direction to create.

Under In a first aspect, the present invention consists in a method for image processing comprising the steps of: generating Image data from many tomographic images and implement a projection process to extract a certain value the image data at a corresponding position of the tomographic images, wherein one ends the projection process after the image data along the direction of the projection process has passed through a first threshold, and if the value comes to a second threshold.

The Procedure themselves with image data generated from ultrasound tomography images MRI tomography images and radiation CT images. The value of each pixel of the image data is the brightness value or the like, which results from the analysis in the imaging, or he is the Echo size, the Flow velocity or the Doppler power value in the case of ultrasound tomography.

This Image processing method generates image data from a tomographic image based on the recombination of NMR received signals or from CT detection signals or based on the analysis of Ultrasonic receive signals. The projection process for the extraction a certain value is executed for each pixel of the image data from many frames (frames of images) to thereby to produce a projected image.

At the Generating a projected image terminates the projection process after the value of the image data for the first time by a threshold along the direction for the occurrence of the value to be extracted has run, and if the value returns to the threshold so that a certain Value (the largest or smallest value), the closer to start the projection process Side (front or back), can be detected; the projection process for the remaining ones Positions will not be carried out.

Accordingly, a more forward or backward pixel on a priority basis detected, and an object that was detected first can certainly are detected, including a surrounding area. Even if there is another object with the greatest or smallest value behind an object is detected in front on a priority basis and information in the depth direction is thus not lost.

consequently may be an image processing method for generating a tomographic image with information in the depth direction can be achieved in a short time.

Under In a second aspect, the present invention is in a Method for image processing, which of the method after the first Point of view is derived, wherein the first and second thresholds the same ones are.

Under In a third aspect, the present invention is in a Device for image processing comprising an image data generating device, the image data is generated from many tomographic images, and one Projection process means, which implements a projection process for extracting a certain value from the image data obtained by the image data generating means are generated at a corresponding one Position of the tomographic images, ending the projection process, after passing the image data along the direction of the projection process has run a first threshold and if the value has become a second threshold comes.

These Image processing device can in a short time a tomographic Image with information in the depth direction in the same way as Create the invention according to the first aspect.

Under In a fourth aspect, the present invention resides in one Device for image processing, by the device after the derived third point of view, where a certain value the greatest value represents.

Under a fifth The point of view of the present invention is a device for image processing, by the device according to the third aspect derived, with a particular value representing the smallest value.

Under In a sixth aspect, the present invention is in a device for image processing by the device is derived according to the third aspect, wherein the first and second thresholds are the same.

Under a seventh aspect, the present invention is in a Device for image processing, by the device after the third aspect is derived, wherein the first threshold greater than the second threshold is.

Under In an eighth aspect, the present invention is in a Device for image processing, by the device after the derived third aspect, which implements the projection process using a lookup table, the addresses as values contains image data pairs, which are to be compared in the course of the projection process, and Output values as comparison results in the form of a table stores.

These Image processing device is able to speed up the projection process to implement, based on the provision of a Look-up table which stores the output values as comparison results in the form of a table, being addressed by comparing in the projection process Values.

Under A ninth aspect of the present invention is in a Device for image processing, by the device after the derived third point of view, and the the projection process under Using a lookup table implements the addresses as values of image data pairs contained during the projection process and output values as comparison results stores in the form of a table, the look-up table having a value to be extracted in the area of the table in case stores the projection process in response on the arrival at the second threshold is terminated.

These Image processing device is designed for implementation of the projection process using a lookup table which the output values as comparison results in the form of a table stores by being addressed via in the projection process to be compared Values, so that the initial value sets to the data of the area to exit of the projection process. Consequently, the institution is in a position the projection process fast to finish without the need for a specialized assessment facility for the End of the procedure.

Corresponding the method based on the reference to a table the output data (the extracted data) is recorded and it becomes the projection process becomes practically completed, even if the projection process is still continuous continues until its completion. The table reference method can be executed become, by the values for assigns even and odd numbers to the (depth) range (range), to take a new value in the continuation of the projection process and for Values of the range for holding a resulting value of the projection process (the projection process becomes for the Rest abandoned).

Under In a tenth aspect, the present invention is in a Ultrasonic examination device containing a receiving device for receiving ultrasonic waves from an examination body as well the image processing apparatus according to the third aspect, wherein the tomographic image that is generated on ultrasound received signals which are supplied by the receiving device.

These Ultrasonic examination device can be a tomographic image with information in the depth direction in a short time in of the same kind as the invention according to the first aspect.

These and other features and advantages of the present invention will become more apparent from the following description of the preferred embodiments the invention in conjunction with the accompanying drawings. Show:

1 a diagram used to explain the conventional ultrasonic imaging method;

2A and 2 B a graph and a curve used to explain the conventional ultrasound imaging method;

3A . 3B and 3C Diagrams used to explain a result of the projection process according to the conventional ultrasound imaging method;

4A . 4B and 4C Diagrams used to explain another result of a projection process according to the conventional ultrasound imaging method;

5 Fig. 10 is a flow chart showing the operational sequence of the image processing method based on a first embodiment of this invention;

6 Fig. 10 is a block diagram showing the principal parts of the image processing apparatus based on the first embodiment of this invention;

7 a graph used to explain the ultrasonic imaging method based on the first embodiment of this invention;

8A . 8B and 8C Diagrams used to explain a resulting image of the ultrasound imaging method based on the first embodiment of this invention;

9A . 9B and 9C Diagrams used to explain another resulting image of the ultrasound imaging method based on the first embodiment of this invention;

10A and 10B Diagrams used to explain a resulting image of the ultrasound imaging method based on the first embodiment of this invention;

11 Fig. 10 is a flow chart showing the operational sequence of the image processing method based on a second embodiment of this invention;

12 a curve used to explain the ultrasonic imaging method based on the second embodiment of this invention;

13 Fig. 10 is a block diagram showing the principal parts of the image processing apparatus based on a third embodiment of this invention;

14 Fig. 10 is a block diagram showing the principal parts of the image processing apparatus based on a fourth embodiment of this invention;

15 Fig. 12 is a block diagram showing the principal parts of the image processing apparatus based on a fifth embodiment of this invention;

16 Fig. 10 is a block diagram showing the principal parts of the image processing apparatus based on a sixth embodiment of the invention;

17 Fig. 12 is a block diagram showing the principal parts of the image processing apparatus based on a seventh embodiment of this invention;

18 Fig. 12 is a block diagram showing the principal arrangement used for the ultrasonic imaging method based on an eighth embodiment of this invention;

19 a diagram explaining a particular arrangement of the look-up table, as used for the ultrasonic imaging method based on the eighth embodiment of this invention, and

20 a curve used to explain the ultrasound imaging method using the look-up table.

The embodiments of the present invention for the special case of ultrasonic tomo The graphs will be explained in detail with reference to the drawings.

(1) execution 1

5 Fig. 11 is a flow chart showing the operational sequence of the image processing method (ultrasonic imaging method) based on the first embodiment of this invention. 6 Fig. 16 is a block diagram showing the arrangement used for the image processing method based on the first embodiment of this invention, and also showing the arrangement of the image processing apparatus (ultrasonic image processing apparatus) based on the first embodiment of this invention. 7 to 10 explain the machining operations in this design.

(1.1) Arrangement of the device for image processing (ultrasound imaging device)

First, the arrangement of the ultrasonic imaging apparatus as the image processing apparatus of this embodiment will be described with reference to FIG 6 described. In the 6 Ultrasonic imaging device shown consists primarily of an ultrasound probe 10 , a transmitting / receiving circuit 20 , a receive beamformer 30 , a Doppler power processor 50 , an image processor 60 , a digital sampling converter 70 and a display or display device 80 ,

The ultrasound probe 10 is an electro-acoustic transducer that converts the electrical transmission signal into an ultrasonic wave to be transmitted to an examination body, and that receives the ultrasonic waves reflected back from the examination body and converts them into electrical signals.

The send / receive circuit 20 amplifies this into the ultrasound probe 10 to be fed transmit signal and demodulates the received echo signals based on a quadrature detection or the like.

The receiver beamformer 30 implements the phase matched summation of the received signals to the Doppler power processor 50 to generate to be applied serial signal.

The Doppler Power Processor 50 implements the quadrature detection for the serial signal to extract signals from moving objects, evaluating the Doppler power value of each pixel.

The image processor 60 implements the projection process for the image data of multiple frames, thereby producing a projected image. The resulting projected image is scanned by the digital scan converter 70 brought to the sampling frequency and to the display device 80 output, which brings the image for display.

The image processor 60 exists, as in 6 is shown from a projection processor 62 as well as a facility 63 for determining the process completion.

The projection processor 62 implements the projection process to extract a specific value from the multiple image records.

The Doppler power processor 50 consists of a quadrature detector 51 which implements the quadrature detection for the serial signal to produce an in-phase component (the 1 component) and a quadrature component (the Q component), further from an MTI processor 52 which extracts signals from moving objects as well as from a power calculator 53 performing the Doppler calculation (I ² + Q ² ) for the 1 component as well as for the Q component to evaluate the Doppler power value P, as in 6 is shown.

(1.2) Process of image processing (Ultrasound imaging procedure)

The operation of the ultrasonic imaging apparatus arranged as described above and the method for the ultrasonic imaging process will be described with reference to the flowchart of FIG 5 explained. In the 5 The embodiment shown illustrates the case for the MIP process for extracting the largest value based on Doppler power imaging by the ultrasound imaging device. The flow of the ultrasound imaging method is divided into the following two main steps 1 and 2.

1st projection process

That of the send / receive circuit 20 amplified transmission signal is sent to the ultrasound probe 10 is applied, which converts the transmission signal into an ultrasonic wave and sends it into an examination body (not shown).

The ultrasonic wave is reflected and scattered in the examination body. Part of the ultrasonic wave returns to the ultrasonic probe 10 by which it is reconverted to an electrical signal (received echo signal) and to the transmitting / receiving circuit 20 is created.

The received echo signal is received by the transmitting / receiving circuit 20 amplified by the receive beamformer 30 phased and summed to the Doppler Power Processor 50 created.

In the Doppler Power Processor 50 separates the quadrature detector 51 the input signal into an I component and a Q component, the MTI processor 52 only extracts signals from moving parts, and the power calculator 53 Evaluates the Doppler power value P of each pixel.

Periodically, image data in the form of the Doppler power value P is generated in synchronization with the emission and reception of the ultrasonic waves. The image processor 60 receives and stores multiple image data sets for use in the later projection process, for example in the memory of the projection processor 62 ,

The projection processor 62 implements the projection process for the stored image data in the form of Doppler power values P. In this embodiment, it executes the projection process of extraction of the largest value for the MIP process for extracting the pieces of large Doppler power values P. In detail, the projection processor selects 62 a pixel to be processed from the image data: (step S1 in FIG 5 ), and starts the MIP process of the Doppler power value P for the selected pixel: (step S2 in FIG 5 ).

2. Assessment of termination of the procedure

Of the Projection process is designed so that he ends after the Doppler power value P of the image data for the first Time by a threshold along the direction for the occurrence of the value to be extracted, and if the value to the Threshold comes back.

Initially, it is checked for the selected pixel whether the threshold flag is already set: (Step S3 in FIG 5 ). The threshold mark representing one bit of a particular register is set to "1" if the selected pixel exceeds the threshold at least once.

If the immediate Doppler power value P is greater than or equal to the threshold, the flag is set: (Steps S4 and S5 in FIG 5 ), or otherwise the threshold mark is left unchanged.

This MIP process is repeated for each selected pixel of all image types along the depth direction: (step S8 in FIG 5 ).

In the case where the threshold mark is already set, the MIP process is repetitively presumed for the selected pixel of all image data along the depth direction that the immediate Doppler power value P is greater than or equal to the threshold: (Steps S6 and S8 in FIG 5 ).

Otherwise, in the event that the threshold mark is already set and the immediate Doppler power value P is less than the threshold, the MIP process is abandoned for the selected pixel: (step S7 in FIG 5 ).

The MIP process continues for the selected pixel of all the image data along the depth direction or, in the case where the MIP process is terminated in accordance with the judgment of the mark, another pixel of the image data is selected to repeat the MIP process , In this way, the MIP process including the judgment of the end of the process takes place for all the pixels of the image data: (step S9 in FIG 5 ).

7 shows the previous procedure. Namely, the projection process is carried out while monitoring the Doppler power value P of the image data, and the process is terminated after the Doppler power value P has passed through the threshold value TH for the first time, and when it is, again by the threshold value TH to run.

When a result of the procedure will be the largest until the end of the projection process detected value as a configured value (configured Doppler Power value P) is output. In the example shown, the peak value the closest to the position at the beginning of the process (at the left end) swelling detected as projected Doppler Power value P, because the projection process for the other swellings or Maxima breaks off at lower positions.

consequently will it be possible the projected Doppler power value P with information in the depth direction provide, based on the priority rule the process start page based, and so the process in a short time to finish.

The ultrasound imaging method described above provides a result of the projection process as described, for example, in U.S. Pat 8A - 8C is shown. When the procedure is performed for a in 8A shown anteriorly extending blood vessel as well as an in 8B Behind the blood vessel shown behind it, at the junction of these blood vessels, the anterior blood vessel is displayed on a priority basis, with the blood vessel behind it remaining hidden behind the anterior blood vessel, as in FIG 8C is shown.

The ultrasound imaging method described above provides a result of the projection process as described in U.S. Pat 9A - 9C for another example is shown. When the procedure is executed for a in 9A shown small dark frontal blood vessel as well as for a in 9B behind it, on a priority basis at the intersection of these blood vessels, the anterior blood vessel is shown, with the bright underlying blood vessel hidden behind the dark anterior blood vessel, as in FIG 9C is shown.

In the case that the projection processor 62 With a look-up table in which output values from the range of the projection process continuation as well as output values from the range are stored differently than even numbers or odd numbers towards the end of the projection process, it is possible to end the process on the basis of the parity test for one or more Bits including the lowest order bit from the output of the projection processor 62 to determine. This system enables easy detection of data belonging to the area for the completion of the projection process, and enables a quick completion of the projection process.

(1.3) Relationship between the threshold and the displayed image

• (1) 8A zeigt ein vorderes Blutgefäß, 8B zeigt ein hinteres Blutgefäß, und 8C zeigt ein resultierendes projiziertes Bild. In diesem Beispiel ist der Schwellenwert TH so eingestellt, daß eine mittels Power Doppler Bildgebung darzustellende Blutströmung richtig ausgewählt wird. Demzufolge fallen der äußere Teil des als vorderer Teil angezeigten Bereichs sowie der Teil, der dahinter verborgen ist, miteinander zusammen.
• (2) 10A zeigt ein Beispiel für den Fall, bei dem der Schwellenwert TH für das Auswählen einer mittels Power Doppler Bildgebung darzustellen Blutströmung kleiner eingestellt ist. In diesem Fall findet, selbst wenn ein kleinerer Doppler Powerwert vorliegt, der Projektionsprozeß nicht tief hinter der Position statt, was in einer Darstellung resultiert, in welcher der Rand des vorderen Blutgefäßes hervorgehoben wird.
• (3) 10B zeigt ein weiteres Beispiel für den Fall, bei dem der Schwellenwert TH für das Auswählen einer mittels Power Doppler Bildgebung darzustellenden Blutströmung auf einen größeren Wert eingestellt ist. In diesem Fall werden kleine Doppler Powerwerte vernachlässigt, so daß lediglich die Blutströmungen mit großen Doppler Powerwerten durch Hervorhebung dargestellt werden.

In general, with blood flow represented by Power Doppler imaging, its Doppler power value P decreases as the position shifts outward. Therefore, a blood vessel is presented in different forms, depending on the threshold value TH used for judgment of the process termination. This process will be in conjunction with the 8A - 8C to 10A - 10B explained.

• (1) 8A shows a frontal blood vessel, 8B shows a posterior blood vessel, and 8C shows a resulting projected image. In this example, the threshold TH is set to properly select a blood flow to be displayed by power Doppler imaging. As a result, the outer part of the area indicated as the front part and the part hidden behind it coincide with each other.
• (2) 10A shows an example of the case where the threshold value TH for selecting a blood flow to be displayed by means of power Doppler imaging is set smaller. In this case, even if there is a smaller Doppler power value, the projection process does not take place deep behind the position, resulting in a representation in which the edge of the anterior blood vessel is highlighted.
• (3) 10B shows another example of the case where the threshold value TH for selecting a blood flow to be displayed by power Doppler imaging is set to a larger value. In this case, small Doppler power values are neglected, so that only the blood flows with large Doppler power values are highlighted.

The Display result varies depending on the selection of the threshold value as illustrated in the above cases (1) - (3) is; and therefore, the threshold value TH is preset to correspond to the intended result, and he can customized to modify the display result.

(2) execution 2

11 FIG. 12 shows the sequence of the MIP process for extracting the largest value based on the power Doppler imaging for the Doppler power value P, which includes a noise component having a substantially constant amplitude or a small movement error or artifact of the subject body.

12 explains the process in the same way as 7 for an example case where the Doppler power value P contains a certain proportion of a noise component or a small motion artifact of the examination body.

The procedure for image data of in 12 quality shown may possibly fail if it is on a single threshold TH, as in 7 shown, based. In particular, the projection process may possibly end erroneously if it encounters a small spike attributable to the noise or artifact.

To cope with this situation, the in. Works 6 shown device having a first threshold TH1 and a second threshold TH2 instead of the single threshold TH. In the case of the MIP process for extracting the largest value, TH1 is set larger than TH2 to provide a hysteresis function, so that the process can stably proceed based on the same principle as the Schmitt (trigger) circuit.

1. projection method

That of the send / receive circuit 20 amplified transmission signal becomes the ultrasonic probe 10 which converts the transmission signal into an ultrasonic wave and transmits it to an examination body (not shown).

The ultrasonic wave is in the Untersu thrown back and scattered. Part of the ultrasonic wave returns to the ultrasonic probe 10 from which they are converted back to an electrical signal (received echo signal) and to the transmitting / receiving circuit 20 to be led.

The received echo signal is received by the transmitting / receiving circuit 20 amplified, by means of the receive beamformer 30 summed up in phase and to the Doppler Power Processor 50 created.

In the Doppler Power processor 50 separates the quadrature detector 51 the input signal into an I component as well as into a Q component, the MTI processor 52 only extracts signals from moving parts, and the power calculator 53 Evaluates the Doppler power value P of each pixel.

It be periodically synchronous with the transmission and reception of the ultrasonic waves Image data as Doppler power value P generated.

The image processor 60 receives and stores multiple image data sets for use in the later projection process, for example in the memory of the projection processor 62 ,

The projection processor 62 implements the projection process for the stored data in the form of Doppler power values P. In this embodiment, he implements the projection process for extracting the largest value for the MIP process for extracting the fractions with large Doppler power values P.

In particular, the projection processor selects 62 a pixel to be processed from the image data: (step S2 in FIG 11 ), and starts the MIP process for the Doppler power value P of the selected pixel: (step S2 in FIG 11 ).

2. Assessment of the process termination

Of the Projection process is designed so that he ends after the Doppler power value P of the image data for the first Over a first threshold TH1 along the direction of existence of the value to be extracted, and if the value is too a second threshold TH2 (TH1> TH2).

Initially, it is checked for the selected pixel whether the threshold mark is already set: (Step S3 in FIG 11 ). The threshold mark representing a bit of a particular register is set to "1" if the selected pixel exceeds the first threshold TH1 at least once.

If the immediate Doppler power value P is greater than or equal to the first threshold TH1, the flag is set: (Steps S4 and S5 in FIG 11 ), or else the threshold value mark is left unchanged.

This MIP process is repeated for selected pixels of all image data in the depth direction: (step S8 in FIG 11 ).

Even in the case where the threshold mark is already set, the MIP process for the selected pixel of all image data along the depth direction is repeatedly assumed that the immediate Doppler power value P is greater than or equal to the second threshold TH2: (Steps S6 and S8 in FIG 11 ).

Otherwise, in the case that the threshold mark is already set and the immediate Doppler power value P is smaller than the second threshold TH2, the MIP process is abandoned for the selected pixel: (step S7 in FIG 11 ).

The MIP process continues for the selected pixel of all the image data along the depth direction or, in the case where the MIP process is terminated in accordance with the judgment of the mark, another pixel of the image data is selected to repeat the MIP process. In this way, the MIP process including evaluation of the process completion takes place for all the pixels of the image data: (step S9 in FIG 11 ).

12 shows the previous procedure. That is, the projection process is carried out while monitoring the Doppler power value P of the image data, and the process is terminated after the Doppler power value P has passed through the first threshold TH1 for the first time and, if the value is, by the second Threshold TH2 to run.

When a result of the procedure will be the largest until the end of the projection process detected value as a projected value (projected Doppler Power value P) is output. In the example shown, the peak value the closest to the process start position lying swelling (at the left end) detected as projected Doppler power value P, because you have the projection process for the remaining swelling breaks off at lower positions.

Of the first threshold TH1 and the second threshold TH2 become so adjusted that they to match the amplitude of the (any) noise, the assessment the process termination not disturbed by the noise and the process can take place accurately.

Consequently will it be possible the projected Doppler power value P with information in the depth direction to provide, based on the priority rule the process start page based, and the process in one short time to finish.

(3) execution 3

The previous first and second embodiments consider the method as well as the facility for an image processing that is designed for the execution of the MIP process for a power Doppler imaging in an ultrasound tomography. The Power Doppler imaging can be done by a so-called B-mode imaging for the execution An ultrasound imaging will be replaced based on the MIP Process or the MinIP process, as explained in the first and second versions.

13 shows the arrangement of the image processing device based on the third embodiment of this invention, which is adapted to the B-mode imaging. In the 13 shown ultrasonic imaging device includes a B-mode processor 40 and performs the projection (MIP or MinIP) process, including the process termination evaluation for a B-mode map generated by the B-mode processor 40 was generated.

These Ultrasonic imaging device performs the MIP process or the MinIP process in accordance with one or more preset thresholds in it Way, like the previous first and second embodiments, and it will be possible the brightness value of the projection or the echo intensity with information in the depth direction, which is on the priority rule at the beginning of the process for one B-mode figure is based, and finish the process in a short time.

Of the first threshold TH1 and the second threshold TH2 become so adjusted that they to match the amplitude of any noise, the assessment the process termination not disturbed by the noise and the process can take place accurately.

(4) execution 4

The previous first and second embodiments consider the method as well as the device for image processing, which is responsible for the execution of the MIP process for the power Doppler imaging are designed, and the previous one third execution represents the for execution of the MIP process or the MinIP process for a B-mode image Image processing device.

The Power Doppler imaging or B-mode imaging can be substituted be through the color flow mapping (CFM color flow mapping) to perform an ultrasound imaging on the MIP process or the MinIP process based, which were explained in the first to third embodiments.

14 shows the arrangement of the image processing apparatus based on the fourth embodiment of this invention.

In the 14 shown ultrasonic imaging device includes a B-mode processor 40 and a Doppler shift processor 50 ' and performs the projection process (MIP or MinIP) including evaluation of the process termination for a Doppler shift image, which is that obtained by the Doppler shift processor 50 ' generated flow velocity reflects. The digital sampling converter 70 sets the B-mode image together from sleep objects as well as the Doppler shift image, and the display device 80 brings the resulting image to presentation.

These Ultrasonic imaging device performs the MIP process or the MinIP process in accordance with one or more preset thresholds in it Way through as the previous first to third embodiments, and it will be possible the projected velocity value with information in the depth direction to provide what is on the priority rule on the beginning of the process for a Doppler shift image is based, and the method may be in one short time to be stopped.

Of the first threshold value TH1 and the second threshold value TN2 adjusted to the amplitude of (any) noise, wherein the assessment of the process termination not disturbed by the noise and the process can to be accurate.

The Setup brings the B-mode image of resting objects by overlaying to indicate what the observation of the periphery of moving Objects allowed.

(5) execution 5

The previous first and second embodiments consider the method as well as the facility for an image processor designed to perform the MIP process for power Doppler Performing imaging, and the previous third embodiment provides one for the execution of the MIP Process or the MinIP process for a B-mode image Device for image processing dar.

Instead of just to display a Power Doppler image or just a B-mode image, Is it possible, to display these images simultaneously via overlay.

15 shows the arrangement of the image processing device based on the fifth embodiment of this invention.

In the 15 shown ultrasonic imaging device includes a B-mode processor 40 and a Doppler shift processor 50 and performs the projection process (MIP or MinIP), including completion of process completion for a Doppler Power image generated by the Doppler Power Processor 50 was generated. The digital sampling converter 70 composes the B-mode image of resting objects as well as the Doppler Power image, and the display device 80 brings the resulting image to the display.

These Ultrasonic imaging device performs the MIP process in correspondence with one or more preset thresholds in it As in the previous first and second embodiments, and it will be possible the projected Doppler power value P with information in the depth direction what is based on the priority rule at the beginning of the process for a Doppler shift image, and the procedure can be in a short Time to be stopped.

Of the first threshold TH1 and the second threshold TH2 become adjusted to the amplitude of (any) noise, wherein the assessment of the process termination not disturbed by the noise and the process can to be accurate.

The Setup shows the B-mode image of sleep objects by overlay and allows the observation of the environment of moving Objects.

(6) execution 6

Even though the previous first to fifth versions the method and the device for image processing related Looking at ultrasound tomography is the innovative image processing also applicable to MRI tomography.

16 shows the arrangement of the MRI device as an image processing apparatus based on the sixth embodiment of this invention.

In the in 16 shown MRI device controls a CPU 110 the operation of the entire MRI device and also controls the transmission / reception of the signals and the re-composition. A transmission circuit 120 generates a radio-frequency pulse used for the MRI device, which is generated by means of a power amplifier 130 amplified and sent to a transmitting coil 140 is created.

When signal reception detects a receiving coil 141 a signal coming from a reception amplifier 150 amplified and then from a receiving circuit 151 is processed. The CPU 110 implements the re-composition process for the received signal to produce the image data from multiple tomographic images. An image processor 160 implements the MIP process for the generated image data, and a display device 180 brings a resulting image to the presentation. The image processor 160 consists of a projection processor 162 and a determination 163 for the process termination, as in 16 is shown.

These MRI facility performs the MIP process in Corresponding to a preset threshold in the same Make out as the previous first run, and it becomes possible to get information to provide in the depth direction, indicating the priority rule on the process start page for a MRI based tomography image is based, and the method can be used in to be finished in a short time.

specially uses this design the tomographic feature of the MRI device, which is the brightness high in the center of the blood vessel is and in which they are to the extent drops how the position turns outward shifts what enables the viewer, the spatial (front / back) Cross-over relationship to recognize running blood vessels.

Of the first threshold TH1 and the second threshold TH2 become adjusted to the amplitude of (any) noise, wherein the assessment of the process termination not disturbed by the noise and the procedure can be accurate.

The function of the image processor 160 can by means of the CPU 110 be achieved on the basis of appropriate software.

(7) execution 7

Even though the previous remarks that Method and the device for image processing related to look at ultrasound tomography as well as MRI tomography, is the image processing according to the invention also applicable to CT tomography.

17 Fig. 10 shows the arrangement of the X-ray CT apparatus as an image processing apparatus based on the seventh embodiment of this invention.

In the in 17 shown device for an X-ray CT provides a frame 201 a mechanical section of the X-ray CT device, in which an X-ray tube 202 and a sensor 203 electrically and mechanically work together to an examining body 205 in different ways to scan or scan.

A table 204 with the examination body placed thereon 205 gets into the frame 201 moved into it. The frame 201 as well as the table 204 are controlled in terms of their tilt angle and the distance movement by a table / frame control 206 , The x-ray tube 202 is controlled for its rotation as well as for the emission of X-rays by an X-ray tube drive control 207 , The sensor or sensor 203 turns around the examination body 205 together with the x-ray tube 202 under the control of a sensor driver 208 ,

The from the x-ray tube 202 outgoing and through the examination body 205 passing x-rays are from the sensor 203 detected and the X-ray data is collected by a data collector (DAS) 209 sampled. The collected data is sent to an image recomposer 210 sent, which reassembles the input data into a picture. The resulting image is displayed on a display device 270 displayed, and the image data is stored in a data memory 212 saved.

The image data is under the control of a system controller 215 from the data store 212 is read out and transferred to the MIP process in accordance with a preset threshold value of an image processor side 260 and the resulting projection image is displayed on the display device 270 brought to the presentation. The image processor 260 consists of a projection processor 262 and a process end determination 263 , as in 17 is shown.

Image data from many tomographic images generated by the data collection and the image re-composition are retrieved from the data memory 212 The MIP process with a preset threshold is executed for the data in the same way as in the previous first embodiment. The implementation of the MIP process makes it possible to provide information in the depth direction, based on the priority rule on the process start side for a tomographic image generated by the X-ray CT apparatus, and the method can be completed in a short time.

Consequently allows the procedure allows the viewer to intersect the spatial relation Recognize organs by using the feature of roentgen CT imaging, in which organs, such as a bile duct, in her outer section darker than in the center.

in addition come on that an application of the property of tomography with assistance by a contrast agent in which the brightness in the center of a blood vessel is large and falls to the extent that the position is outward shifts the viewer, the spatial Recognize the relation (front / back) of crossing blood vessels.

Of the first threshold TH1 and the second threshold TH2 become adjusted to the amplitude of (any) noise, wherein the assessment of the process termination not disturbed by the noise and the method can be accurate as in the case of the second embodiment expire.

(8) execution 8th

18 shows a special hardware arrangement of the image processors 60 . 160 and 260 the previous versions.

The following versions explain an embodiment for the Procedure with a look-up table that allows for the speeding up of the process is thought of by the projection process without the intervention of judgment the process termination continues until completion, and by while of the process holds the final value lets set).

This embodiment is of the type in which the projection process is quickly implemented in a smaller number of steps by using a table device (memory 602 which forms a look-up table) which has addresses as values of image data to be compared with each other and stores output values as comparison results of the image data. The image processors further contain an MPU 601 to access the memory during the projection process, for example during the MIP or MinIP process 602 manufacture.

in the For example, ultrasound imaging is an input signal (NEW) a new Doppler power value P and another input signal (ALT) of the immediately preceding Doppler power value P as one Addressing for given the table.

The following explanations explain a table that stores such data in order for the Projek After the image data has passed through the threshold along the direction of existence of the value to be extracted (ascending direction for the MIP process or descending direction for the MinIP process) for the first time, and when the value returns to the threshold (in the descending direction for the MIP process or in the ascending direction for the MinIP process). The threshold includes a first threshold (TH1) and a second threshold (TH2).

These execution is for that designed to assign even numbers to the values in the range where the projection process is progressing, to accept a new value, and odd numbers for values assign the area where resulting values of the projection process be held (the projection process is interrupted afterwards). Instead of assigning even numbers to the values in process execution and of odd numbers for the values when settling, can be the assignment of even numbers as well as odd numbers also be reversed. The allocation of only an even number or odd number for a value produces an error of 1, which is practically negligible is when the brightness has 64 or 256 tints.

• (1) Für ALT mit gerader Zahl
• ➀ für ALT kleiner als TH1 Den größeren Wert von NEU und ALT, wobei sein LSB bzw. niederwertigstes Bit aufgehoben wird, so daß er gerade ist.
• ➁ für ALT größer oder gleich TH1
• a) für NEU größer als TH2 Den größeren Wert von NEU und ALT, wobei sein LSB bzw. niederwertigstes Bit aufgehoben wird, so daß er gerade ist.
• b) für NEU kleiner als TH2 ALT addiert mit 1, so daß er ungerade ist.
• (2) Für ALT mit ungerader Zahl ALT ohne Rücksicht auf TH1 und TH2. Ein Ausgangswert als ungerade Zahl bedeutet das Ende des Verfahrens.

The lookup table has contents (output values) as follows.

• (1) For ALT with even number
• ➀ for ALT less than TH1 The greater of NEW and ALT, with its LSB or least significant bit being canceled so that it is even.
• ➁ for ALT greater than or equal to TH1
• a) for NEW greater than TH2 The larger value of NEW and ALT, with its LSB or least significant bit being canceled so that it is even.
• b) for NEW, less than TH2 ALT adds 1, so it is odd.
• (2) For ALT with odd number ALT regardless of TH1 and TH2. An output value as an odd number means the end of the procedure.

19 Fig. 13 shows a concrete example of the look-up table as a 16x16 matrix formed according to the above-mentioned criteria. The Doppler power value P ranges from 0 to 15 and the values for TH1 and TH2 are set to 8 and 6, respectively.

Of the on the above mentioned Lookup table based projection process generates output values even numbers for the above case (1) ➀ and the next case (1) ➁a, and subsequently to the case (1) ➁b, it holds the odd-numbered one Initial value as a case structure for the case (2), which one the priority scheme for the Result of the projection process for a forward object implemented. The settling of the output data brings the projection process too his end.

The method based on the look-up table is described in detail in connection with 19 as well as with 20 explained in more detail.

In In this example, the introduced size takes NEW consecutively the values 04, 06, 08, 10, 08, 06, 04, 10, 12, 05, 07, 12, 13, 15 and 07 on; the size ALT has one Initial value of 00 on; and the threshold values TH1 and TH2 are set to 8 or 6 respectively.

Step S1 generates data in the case design area (1) ➀ in 19 (Range of S1 in 20 ).
NEW = 04 and ALT = 00 gives output 04
NEW = 06 and ALT = 04 gives output 06
NEW = 08 and ALT = 06 gives output 08

Step S2 generates data in the area for case design (1) ➁a in 19 (Range of S2 in 20 ).
NEW = 10 and ALT = 08 gives output 10
NEW = 08 and ALT = 10 gives output 10

Step S3 holds data in the case design area (1) ➁b in FIG 19 (Range of S3 in 20 ).
NEW = 06 and ALT = 10 gives output 10
NEW = 04 and ALT = 10 gives output 11

Step S4 holds data in the case design area (FIG. 2 ) in 19 (Range of S4 in 20 ).
NEW = 10 and ALT = 11 gives output 11
NEW = 12 and ALT = 11 gives output 11
NEW = 05 and ALT = 11 gives output 11
NEW = 07 and ALT = 11 gives output 11
NEW = 12 and ALT = 11 gives output 11
NEW = 13 and ALT = 11 gives output 11
NEW = 15 and ALT = 11 gives output 11
NEW = 07 and ALT = 11 gives output 11

The exit 11 For the largest value, 10 is in the range of step 2 and the process goes to the state where the output value does not change even if the process continues to run.

As a result of this method, it becomes possible for the projection process to provide the projection result with information in the depth direction, which is based on some rule, and the Eliminate need for specialized hardware and software tools to assess completion of the procedure. Based on the simple table lookup method (spreadsheet), the method can be run in a smaller number of steps (with the same number of steps as in the conventional system).

According to this Table lookup methods will be output (to be extracted) Data is held even when the projection process by Conclusion continues, and this is practically the end of the projection process.

By doing the look-up table with a RAM, a so-called. Flash memory or the like, it becomes possible to arbitrarily add the table contents a freely selectable To revise or change the time when the device starts up.

Even though the previous embodiments examples for represent the MIP process, the greatest value extracted, can they are also applied to the MinIP process, which uses the extracted smallest value. The extraction of the smallest value can using the MIP process based on the inversion of the values accomplished become.

Claims (10)

Image processing method comprising the steps: Produce from image data from many tomographic images and To implement a projection process to extract a certain value the image data at a corresponding position of the tomographic images, marked by After completing the projection process the image data along a direction of the projection process has passed through a first threshold and if the value comes to a second threshold. An image processing method according to claim 1, wherein the first and second thresholds are the same. An image processing device comprising: an image data generating device ( 10 . 20 . 30 . 50 ), which generates image data from many tomographic images, and a projection process device ( 62 . 63 ) implementing a projection process for extracting a certain value from the image data generated by the image data generating means at a corresponding position of the tomographic images, characterized by terminating the projection process after the image data value along a direction of the projection process by a first threshold value has run and if the value comes to a second threshold. An image processing apparatus according to claim 3, wherein the certain value the biggest value is. An image processing apparatus according to claim 3, wherein the certain value is the smallest value. An image processing apparatus according to claim 3, wherein the first and second thresholds are the same. An image processing apparatus according to claim 3, wherein the first threshold is greater than the second threshold is. Image processing device according to claim 3, the the projection process using a lookup table implemented, which contains addresses as values of image data pairs, the while of the projection process and output values stores as comparison results in the form of a table. Image processing device according to claim 3, the the projection process using a lookup table implemented, which contains addresses as values of image data pairs, the while of the projection process and output values stores as comparison results in the form of a table, wherein the look up table has a value to be extracted in the range of Table for stores the case that the Projection process in response to the arrival at the second threshold is ended. Containing ultrasonic examination device a receiving device for receiving ultrasonic waves from an examination body and The image processing device according to claim 3, wherein the tomographic Image that is generated based on received ultrasound signals, which are supplied by the receiving device.