Diagnostic imaging apparatus

Abstract: A CT scanner (10) generates views of data such as equal angular increment detector fan views (Figure 2A) which are convolved or filtered by an array processor (24). A combined backprojector and forward projector (28) backprojects the data from the array processor into an output memory (30) and forward projects lines of image representation data from an input memory (26) to the output memory. Each view representation may again be an equal angular increment detector fan format view (Figure 2A), a parallel ray format view (Figure 2B), an equal linear increment source fan format view (Figure 2D), a source fan format view (Figure 2C), an equal angular incremental detector fan format view (Figure 2E), an equal linear increment detector fan format view (Figure 2F), or an equal angular increment source fan format view (Figure 2G). In a backprojector mode, the projector is addressed by line and row addresses of a pixel of the output memory. A look-up table (76) and a multiplier (82) generate a weighting function (W). A multiplier (78) and an adding means (80) along with the look-up table convert the memory addresses into an appropriate address for a line of view data stored in a projector memory (60). An element of view data retrieved in response to the received address is multiplied (84) by the weighting function. In a forward projector mode, a parallel ray forward projection configuration (92) is provided. A view format transform assembly (90) transforms other format view designations and addresses into the corresponding parallel ray format view designations and addresses.

Description: This invention relates to diagnostic imaging apparatus. It finds particular application in conjunction with computed tomography (CT) scanners and will be described with particular reference thereto. However, it is to be appreciated that the invention may also find application in conjunction with magnetic resonance, positron emission, and other types of diagnostic imaging apparatus. Heretofore, CT scanners have defined an examination region or scan circle in which the patient or other subject to be imaged was disposed. A beam of radiation was transmitted across the scan circle from an x-ray source to oppositely disposed radiation detectors. The segment of the beam impinging on a sampled detector defines a ray extending between the source and the sampled detector. The source or beam of radiation was rotated around the scan circle such that data from a multiplicity of rays crisscrossing the scan circle were collected. The sampled data was convolved and backprojected into an image memory which was commonly described as a two dimensional array of memory elements. Each memory element stored a CT number indicative of the transmission or attenuation of the rays attributable to a corresponding incremental element within the scan circle. The data from each ray which crossed a given incremental element of the scan circle contributed to the corresponding CT number, i.e. the CT number for each memory element of the resultant image was the sum of contributions from the multiplicity of rays which passed through the corresponding incremental element of the scan circle. Most commonly, the x-ray data was transformed into the image representation utilizing filtered backprojection. A family of rays was assembled into a view. Each view was filtered or convolved with a filter function and backprojected into the image memory. Various view geometries have been utilized in this process. As one example, each view was composed of the data corresponding to rays passing parallel to each other through the scan circle, such as from a traverse and rotate type scanner. In a rotating fan beam type scanner in which both the source and detectors rotate, each view could be made up of concurrent samplings of the detectors which span the x-ray beam when the x-ray source was in a given position, i.e. a source fan view. The detector commonly had either an equal linear spacing or an equal angular spacing. Alternately with a stationary detector rotating source geometry, a detector fan view could be formed from the rays received by a single detector as the x-ray source passed in back of the scan circle from that detector. In forward projection, the image data was processed to synthesize each of the multiplicity of views that went through convolution and backprojection to make the image representation. Various backprojection and forward projection algorithms have been developed. CT scanner customers normally demand a substantially instantaneous display of the resultant CT image. To obtain the image representation rapidly, the backprojection was normally performed with dedicated backprojection hardware. The many millions of computations required rendered general purpose computers inappropriately slow for backprojection. Various forward projection software routines have been written for general purpose minicomputers. However, the task of breaking the image representation apart into its component parts again requires many millions of computations. The execution time for such programs, commonly on the order of many minutes to hours, render forward projection too slow for many every day clinical applications. US-A-222104 discloses an apparatus for examining a body slice by means of penetrating radiation such as x-radiation, the apparatus including a scanning arrangement having means for projecting the radiation through the body slice and means for detecting the intensity of the radiation after passage through the body and for providing sets of data signals where each set represents the attenuation of the radiation along individual directions which are at different angles with respect to the body within a fan-shaped distribution of directions and different sets represent the attenuation of the radiation along such individual directions within fan-shaped distributions which are at different mean angles relative to the body; means for modifying the data signals by combination with other data signals of the same set; means for interpolating between the modified data signals to provide data signals relating to a larger number of directions angularly spaced in the respective fan-shaped distribution; storage means having a plurality of storage locations corresponding to elements of a matrix of elements notionally defined in said slice; means for back projecting the original and interpolated data signals onto storage locations corresponding to elements intersected by the respective directions; means for forward projection from the storage locations corresponding to elements intersected by sets of parallel directions defined in said slice, where different sets of such parallel directions are at different angles relative to the body, to provide attenuation data for those parallel directions; means for correcting the attenuation data for the sets of parallel directions for errors relating to the distribution of attenuation in different parts of the slice; and means for back projecting the corrected attenuation data for the sets of parallel directions to storage locations corresponding to elements of the matrix intersected by said sets of parallel directions to provide a representation of the distribution of attenuation in said slice. It is an object of the present invention to provide a diagnostic imaging apparatus wherein these problems are alleviated. According to the invention there is provided a diagnostic imaging apparatus comprising: a CT scanner for generating views of radiation intensity data, each view including view data elements which correspond to an intensity of radiation along a corresponding ray through a scan circle; and an array processor means for processing a plurality of views; characterised by a combined backprojector and forward projector means for backprojecting processed views into an image representation and for forward projecting data of an image representation into view representations, the combined backprojector and forward projector means including a projector memory means for receiving lines of data, in a backprojecting mode the lines of data being view data lines and in a forward projecting mode the lines of data being lines of the image representation; and a weighting function multiplying means for multiplying each data value retrieved from the projector memory by a weighting function. One advantage of the present invention is its speed. Not only is backprojection accomplished at a rapid speed, but forward projection can be accomplished in less than ten seconds. Another advantage of the present invention is that it enables medical personnel to implement image enhancement techniques previously only available for other view formats or for images reconstructed from other imaging modalities. Another advantage of the present invention is that it is component-efficient. It enables filtered backprojection and forward projection techniques to be accomplished with less circuitry and hardware than prior art backprojectors. One diagnostic imaging apparatus in accordance with the invention will now be described by way of example with reference to the accompanying drawings in which: Figure 1 is a diagrammatic illustration of the diagnostic imaging apparatus; Figures 2A, 2B, 2C, 2D, 2E, 2F and 2G are illustrative of detector fan with equal angular increments, parallel ray, source fan with equal angular increments, source fan with equal linear increments, detector fan with equal angular increments, detector fan with equal linear increments and source fan with equal angular increments, view formats, respectively; Figure 3 is illustrative of the relative geometries of the image memory and scanner geometry incorporating the geometric terms and relationships referenced in Equations (1) through (16); Figure 4 is a diagrammatic illustration of details of a backprojector configuration of the combined back/forward projector of Figure 1; and, Figure 5 is a diagrammatic illustration of the forward projector configuration of the combined back/forward projector of Figure 1. With reference to Figure 1, a CT scanner 10 includes an x-ray source or tube 12 for irradiating a scan circle 14 with a beam of radiation. An array of detectors 16 are disposed across the scan circle opposite from the x-ray source. In the preferred embodiment, the x-ray detectors include a stationary detector array completely circumscribing the scan circle. An x-ray beam rotating means 18, such as a motor and drive belt arrangement, rotates the beam of radiation around the scan circle. In the preferred embodiment, the x-ray beam rotating means includes a drive motor which rotates a gantry on which the x-ray tube is mounted continuously around the scan circle. A sampling means 20 repeatedly samples the output of at least the detectors which are irradiated by the x-ray beam and receives an indication of the angular position of the x-ray source during the sampling. An array of buffer memories 22 store the data sampled by the sampling means. With reference to FIGURE 2A, the buffers in a preferred architecture each store the data from one of the irradiated detectors until the buffer holds a plurality of view data elements each corresponding to one of the rays of the detector fan view. The detector fan data is interpolated to correspond to one of the formats of FIGURES 2B-2G, preferably, the equal angular increment of FIGURE 2E or the equal linear increment of FIGURE 2F. Views of other formats, such as those illustrated in FIGURES 2A-2G as are known in the art, may also be directly collected or interpolated from the collected data. An array processor 24 processes each view of data as is conventional in the art and loads them into an input memory 26 . More specifically, the array processor performs mathematical manipulations which convolve each view with a filter or convolution function. Numerous filter and convolution functions appropriate to each view format and for various imaging protocols are known in the art. A combined backprojecting and forward projecting means 28 backprojects each received view into pixels or memory elements (x,y) of an output memory 30 . During the backprojection, the view data are converted into a weighted value for each memory element of the image memory and summed into the data previously stored in the same memory element. A display means 32 , such as a video monitor, displays the reconstructed image representation in the output memory. Alternately, the image representation may be stored on a tape or disk storage means 34 , subject to other processing, or the like. The backprojecting /forward projecting means 28 under the control of an operator console 36 selectively forward projects image data loaded into the input memory 26 into corresponding pixels of lines of the output memory means 30 . The console configures the forward projecting means such that the resultant view representations stored in the output memory means correspond to source fan format views, detector fan format views, equal angular or linear increment format views, parallel ray format views, or the like. A view processing means 40 operates on the reconstructed views with conventional view processing techniques. For example, the view processing means may cause single, individual views to be displayed on the video monitor 32 or stored in the tape or disk memory 34 . Alternately, the view processing means may convey the view representations to a view data adjusting means 42 which operates on the data of each view with conventional filter or correction functions, such as a bone hardness correction algorithm or the like. The filtered or corrected views are further operated upon by the view processing means to be altered and stored, as may be appropriate for the configuration of the array processor 24 . Alternately, the view processing means may perform an appropriate filter or convolution operation for the selected view format. The view processor transforms the altered views to the view format for which the array processor and backprojector are projected. The views are returned to the input of the array processor convolved and backprojected into a revised or adjusted image representation. If the altered views are already convolved, the set view representations are loaded into the input memory 26 and backprojected. Optionally, an additional imaging modality 50 , such as a magnetic resonance imaging apparatus, a PET scanner, digital x-ray apparatus, or the like may also generate image data. An image reconstruction means 52 implements an appropriate algorithm for the imaging modality of imager 50 to reconstruct image representations. The image representations are loaded directly into the input memory 26 . Alternately, the second modality image representations may be stored on tape or disk and later loaded into the input memory 26 . This enables the image representations from other imaging modalities to be forward projected into the corresponding views that would have been produced by a CT scanner and to be corrected or processed with CT scanner filters, correction algorithms, or the like. With reference to FIGURES 3 and 4, the output memory 30 when configured to receive an image representation is conceptualized as a rectangular array of memory elements which are denoted by the rectangular coordinates (x,y). The (x,y) coordinate system is rotated through an angle γ to form a second coordinate system (u,v). The (u,v) coordinate system has the same origin, i.e. center of the image circle, as the (x,y) coordinate system. The v axis is coincident with a line extending from the vertex of the fan data to the origin. The backprojector receives each view  from the array processor and temporarily stores it in a projector memory means 60 . Each view includes a one dimensional array of view data elements U. The relationship between the view data address U and the image coordinates u and v is given by the relationship: U = D D-v u where the dimension D is defined in FIGURE 3. Each view data element is weighted before being added to the corresponding elements of the image representation in the output memory. A weighting function W is defined by: W = D 2 D-v where the geometric relationships are again defined by FIGURE 3. In the backprojecting mode, memories 62 and 64 contain the parameters of Table 1. Backprojection MEM 1 = u o MEM 2 = Δu x MEM 3 = Δu y MEM 5 = v o MEM 6 = Δv x MEM 7 = Δv y Initial values of u and v, u o and v o respectively correspond to the initial image coordinates pixel address x o and y o . Typically, the image row address x is incremented from one end to the other. Then, the column and address y is incremented and the end to end x incrementation is repeated. This process is continued until the last image column and row address is reached. Each time x is incremented, the u and v values are generated by incrementing Δu x and Δv x , respectively. Thus, u(new) = u(old) + Δu x v(new) = v(old) + Δv x Likewise, when y is incremented the u and v values are: u(new) = u(old) + Δu y v(new) = v(old) + Δv 2 y A register 66 stores the u value and an adder 68 selectively increments the u value by one of Δu x and Δu y . Analogously, a register 70 stores the v value and an adder 72 selectively increments the v value by one of Δu x and Δv y . A control means 74 controls the loading of memories 62 and 64 in accordance with Table 1. Columns and rows may, of course, be reversed. A look-up table 76 is preprogrammed to be addressed by the value v and retrieve the corresponding value (D/(D-v)). The value of D is, of course, a constant for a given CT scanner. A projector memory address generating means includes a multiplying means 78 which multiplies each value of u by the D/(D-v) value. An adding means 80 adds a centering constant as may be appropriate to bring the center of the scan circle and the center of the image memory into coincidence. The projector memory 60 is addressed with this value to retrieve the corresponding view data element. A multiplying means 82 multiplies the D/(D-v) value by itself, i.e. squares the value, to generate the weighting factor W. A multiplying means 84 multiplies the retrieved view data element by this weighting function. This process is repeated until the appropriate contribution from each element of the view has been made to each memory element the image representation of the output memory. The projector memory 60 is then reloaded with the next line of data, i.e. the next convolved view from the array processor and memories 62 , 64 are loaded with the next values of u o , Δu x , Δu y , Δv x , Δv y and the process is repeated. With reference to FIGURE 5, in a forward projecting mode, the projector memory 60 is loaded with one line of the image data from the input memory 26 , which may be expanded or interpolated as necessary. The output memory 30 accumulates the synthesized view data. The forward projector consists of two basic sections - a first section 90 and a view synthesizing means 92 . The first section 90 determines the view format. It transforms the view designations and addresses of other formats into standard , t format used by the view synthesizing means 92 . Specifically, the view format is determined by the values loaded into memories 62 and 64 and look-up tables 104 and 106 , and the interconnect configuration of the first section 90 as controlled by the control means 74 . Tables 2, 3, 4, and 5 tabulate the values loaded into memories 62 and 64 . Forward Projecting (Parallel) MEM 1 = t o MEM 2 = Δt MEM 3 = na MEM 5 =  MEM 6 = Δ MEM 7 = na Forward Projecting (fan equal angular increment) MEM 1 = α o MEM 2 = Δα MEM 3 = na MEM 5 = γ o MEM 6 = Δγ MEM 7 = na Forward Projecting (fan equal linear increment) MEM 1 = U o MEM 2 = ΔU MEM 3 = na MEM 5 = γ o MEM 6 = Δγ MEM 7 = na Forward Proj (det. fans, equal source angl incremented MEM 1 = γ o + ε o MEM 2 = Δε MEM 3 = Δγ MEM 5 = γ 0 MEM 6 = Δ γ MEM 7 = na The view synthesizing means 92 accepts inputs from the first section 90 and generates the contribution to the views stored in the output memory 30 . In the parallel ray format view of FIGURE 2B, each view is denoted by its angular position . Each element of data within the view is denoted by its position therealong t. The forward projector retrieves the corresponding data value from each data row as described by the relationship: x = t cos + S tan The weighting factor for each retrieved data value from the image memory line is weighted by a weighting value W: W = 1 cos Each line of image data is loaded into the projector input memory 60 . The values of the data positions t along a selected view  are incremented until the appropriate data from the stored image data row is provided for each data element of the view . The view  is then incremented by one and each of its addresses t cyclically addressed. This process is repeated until the weighted data values from the first image data line are forward projected into the appropriate data elements of each view. Then, a second line of image data is loaded into the projector memory means 60 , the memories 62 and 64 are loaded with the next values, and the incrementing of the data positions t and views is repeated. To implement these forward projection relationships, the memory, multiplier, and adder components of FIGURE 5 are reconfigured by the control means 74 . A look-up table means includes a look-up table 100 that is loaded with the values of 1/cos and a second look-up table 102 is loaded with the values of tan. Although the cosine and tangent values may be calculated, the use of look-up tables improves processing speed. The projector memory addresses generating means which includes the multiplying means 78 which multiplies the t view element address by the retrieved 1/cos value. The multiplying means 82 multiplies the tan value by the position S of the data line in the image representation. In the illustrated embodiment in which rows are loaded, the position S is indicative of its row of data in projector memory. The adding means 80 adds the S tan value to the product from the multiplier 78 to create the address x of a data line stored in the projector memory means 60 . Typically, in actual operation, first view data is synthesized for over the range of ±45°. When this limit is exceeded, image column data is loaded into projector memory 60 . The distance S is now measured from the y axis, and γ is measured from the x axis. FIGURE 3 is valid if the y axis is changed to the x axis and the x axis is changed to the y axis. The operator can also select to forward project the data into equal angle detector fan format views as illustrated in FIGURE 2A. Each equal angular increment detector fan format view is denoted by its angular position γ around the scan circle and the data along each view is denoted by the angular positions α of the rays of the view. The format means 90 generates the γ, addresses and transforms them into equivalent parallel ,t addresses for the view synthesizing means 92 . The parallel ray format view designation and view addresses t are related to the equal angular increment detector fan format view designation and addresses γ and α by: t = D sin α  = γ - α The memory data line address x and the weighting value W of Equations (7) and (8) in the equal angular increment detector fan format become: x = t cos + S tan = D sinα cos(γ-α) + S tan(γ-α) W = 1 cos = 1 cos(γ-α) The address α is converted to a value that can replace the t address by a look-up table 104 . A look-up table 106 which looks up the corresponding value of D sinα. A subtraction means 108 subtracts the view address α from the view designation γ to generate the value equivalent to  of the view synthesizing means. The values of t and then address the view synthesizing means 92 as described above. When collecting fan data with equal linear increments as illustrated in FIGURE 2D, each view is denoted by its angular position γ around the scan circle and the linear increment U along each view. The position along each equal linear increment fan data format view is related to the address t of the parallel ray format view and the view angle position γ is related to the angular position  of parallel ray format views by the relationships: t = UD U 2 + D 2 1/2 = γ - tan -1 U D Inserting these equations into the relationship of Equations 7 and 8, the address x of the image data line in the backprojector memory 60 and the weighting factor W become: x = U + S(sinγ - (U/D)cosγ) cos γ +(U/D)sinγ W = (1+(U/D) 2 ) 1/2 cosγ+(U/D)sinγ The format transform means look-up table 104 converts each data position U along one of the views to the corresponding t address. Specifically, the look-up table 104 is preprogrammed in accordance with Equation (13). The look-up table 106 determines the tan -1 (U/D) value and the subtraction means 108 subtracts this quantity from the view angle γ to generate the  equivalent value for the second forward projector input. The forward projector can also be configured to project detector fan format views with equal angular source increments as illustrated in FIGURE 2G. Each view is denoted by the angular source position ε and each view data element is designated by its angular increment γ. The equivalent values for the parallel ray format view designation  and data address t are related to γ and ε by: t = DR sin(γ+ε) (R 2 + D 2 + 2DRcos(γ+ε)) 1/2 = γ - tan -1 Rsin(γ + ε) D+R cos(γ + ε) Inserting these relationships into Equations (7) and (8), the data line address x and the weighting factor W become: x = DRsin(γ+ε) + S(Dsinγ - Rsinε) Dcosγ + Rcosε W = (R 2 + D 2 + 2DR cos(γ + ε) 1/2 Dcosγ + Rcosε The memory 62 , adder 68 , and register 66 generate the angle γ + ε. The look-up table 104 is addressed by the (γ+ε) sum to retrieve a corresponding value precalculated in accordance with Equation (17) as the corresponding t address. The other look-up table 104 is preprogrammed in accordance with the inverse tangent portion of Equation (18). Each time the position along the data line is incremented, the look-up table 106 is addressed by the new (γ +ε) term to retrieve the corresponding inverse tangent function which is subtracted from the value of γ by the subtraction means 108 to generate a view designation equivalent to the parallel ray view designation or angle. In the described preferred embodiment, the forward projector algorithm is based on parallel ray geometry. The format transforming means adjusts for other view formats, such as source fan views, detector fan views, equal angle views, equal linear increment views, and the like. The view synthesizing means 92 may function in any one of these or other view formats. To accommodate the other view formats, the format transforming means may reverse some of the algorithms, combine algorithms, or the like as is appropriate to transform the selected view formats into the format selected for use in the view synthesizing means 92 .

Claims: A diagnostic imaging apparatus comprising: a CT scanner (10) for generating views of radiation intensity data, each view including view data elements which correspond to an intensity of radiation along a corresponding ray through a scan circle (14); and an array processor means (24) for processing a plurality of views; characterised by a combined backprojector and forward projector means (28) for backprojecting processed views into an image representation and for forward projecting data of an image representation into view representations, the combined backprojector and forward projector means (28) including a projector memory means (60) for receiving lines of data, in a backprojecting mode the lines of data being view data lines and in a forward projecting mode the lines of data being lines of the image representation; and a weighting function multiplying means (84) for multiplying each data value retrieved from the projector memory by a weighting function (W). An apparatus according to Claim 1 further including: a non-invasive examination means (50) for generating diagnostic data indicative of interior regions of a subject; an image reconstruction means (52) for reconstructing the diagnostic data into an image representation, the reconstruction means (52) being operatively connected with an input memory (26) which is connected with an input of the combined backprojector and forward projector means (28) for selectively loading the image representation into the input memory (26), whereby image representations from scanners other than CT scanners can be converted into CT scanner view representations. An apparatus according to Claim 1 or Claim 2 further including a view representation adjusting means (42) for adjusting view representations in accordance with a preselected algorithm, the view representation adjusting means (42) being operatively connected with an output memory means (30) for receiving forward projected view representations therefrom and being operatively connected with at least one of the array processor (24) and combined backprojection and forward projection means (28) for supplying the adjusted view representations thereto to be backprojected into an adjusted image representation. An apparatus according to any one of Claims 1 to 3 wherein the combined backprojector and forward projector means (28) further includes: first and second inputs for receiving projected data line designations and data addresses (u, v or t, ) for a data element within each projected line for one of an image data line and a view data line; a memory address generating means (78) operatively connected with the inputs for generating an address of a data element in the other of the image data and view data line stored in the projector memory means (60); and, a weighting function generating means (76, 82 or 100) operatively connected with the first and second inputs for generating a weighting function (W) from the projected line designations and addresses, the weighting function generating means (76, 82 or 100) being operatively connected with the weighting function multiplying means (84). An apparatus according to any one of the preceding claims further including: a look-up table means (100, 102) which is addressed by a view angle designation to retrieve values 1/cos and tan0, the look-up table means (100) being operatively connected with the weighting function multiplying means (84) for conveying the 1/cos value thereto; a second multiplying means (78) for multiplying a view data element address designation (t) by the 1/cos term; a third multiplying means (82) for multiplying the tan term by a function (S) of a position of an image data line stored in the projector memory means (60) relative to the image representation; and, an adding means (80) operatively connected with the second and third multiplying means (78, 82) for adding the outputs thereof and being operatively connected with the projector memory means (60) for addressing the line of image data therein. An apparatus according to Claim 5, wherein the view angle designation is an indication of an angle of a parallel ray format view and the view data element address (t) is a designation of one of the parallel rays of the view and further including a view format transforming means (90) for transforming view designations and addresses of other view formats into an equivalent of a parallel ray format view designation and data element addresses. An apparatus according to Claim 6, wherein the view format transforming means (90) includes at least one of: a means for transforming equal linear increment fan format view designations and addresses into parallel ray format view designations and addresses; a means for transforming equal angular increment detector fan format view designations and addresses into parallel ray format view designations and addresses; and, a means for transforming equal angular increment source fan format view designations and addresses into parallel ray format view designations and addresses. An apparatus according to Claim 1 further including: in a backprojecting configuration, first and second inputs for receiving image memory row and column addresses (u, v); a memory address generating means (78) for generating addresses of view elements of each view data line stored in the projector memory means (60) from the image memory row and column addresses (u, v); a weighting function generating means (76, 82) for generating the weighting function (W) from the image memory row and column addresses (u, v), the weighting function generating means (76, 82) being operatively connected with the weighting function multiplying means (84).

Inventors: BRUNNETT CARL J, HEIPLE HOLLY C, ZACHARY ALLEN B, BRUNNETT, CARL J., HEIPLE, HOLLY C., ZACHARY, ALLEN B.
Applicants: PICKER INT INC, PICKER INTERNATIONAL, INC.
Application year: 1989
Main classification: G06T1
IPC codes: G06T1, G06T11, A61B6