METHOD AND APPARATUS FOR PRODUCING ULTRASOUND IMAGES

Abstract: The values of two parameters at a plurality of points in an ultrasound image are disployed. The intensity of each pixel in the display (100) is modulated in accordance with the instantaneous amplitude of the detected echoes at corresponding points in the image. The hue of each pixel is modulated to a first color whenever the value of the instantaneous frequency of the echoes at the corresponding point in the image is greater than a reference value and to a second color whenever the value of the instantaneous frequency is less than the reference value. The saturation at each pixel is modulated as a function of the absolute value of the deviation of the frequency from the reference value at the corresponding point in the image.

Description: The invention relates to a method for displaying a diagnostic ultrasound image comprising the steps of : directing pulses of ultrasound energy into a body and detecting echoes of the energy which are reflected from structures within the body; producing a first signal which corresponds to the instantaneous amplitude of the detected echoes; producing an image in which each pixel maps the location of the point of origin of a corresponding echo within the body; modulating the intensity of each pixel with the first signal produced from the corresponding echo. The invention also relates to an ultrasound imaging apparatus comprising: a transducer arrangement associated with a transmitter for directing a beam of ultrasound energy into a region of a body and with a receiver for detecting echoes of the energy which are reflected from structures within the body; an AM detector for producing a first signal, a(x,y), which represents the instantaneous amplitude of the detected echoes: a colour display unit; a control unit for scanning the beam with respect to the body and for controlling the display unit so that it produces an image wherein the position of each pixel maps the point of origin of corresponding echoes in the body; and an intensity modulator for modulating the intensity of each pixel with corresponding values of the first signal. In medical ultrasound, conventional pulsed-echo instruments display a monochrome image of the envelope of the RF echo signal which is returned from the body. Isolated point scatterers and large, reflecting interfaces thus show up as points or lines. The image represents a slice which is perpendicular to a plane swept out by the ulrasound beam. The resolution cell is formed by the RF pulse length (in the axial direction) and the diffraction limited lateral focus of the transducer aperture after any propagation distortions (attributable for example to refractive index variations in the body). Living human tissue possesses a significant frequency dependent attenuation characteristic which is normally modeled, (to a first appoximation) in healthy liver tissue, as linear with a slope of approximately 0.5 db/cm/MHz. As an example, at 3 MHz, the attenuation for a "normal" human liver tissue is 1.5 db/cm in each direction or 3 db/cm for round trip pulse echoes. A 20 cm path depth thus requires a time-gain-compensation (TGC) amplifier with a 60 db gain increase over the time of the return signals after the transmit pulse. When a broadband RF pulse is transmitted, lower frequency components of the signal are attenuated less than the high frequency components. Thus the spectral centroid (and hence the average instantaneous frequency) of the echoes shifts downwards as a function of the depth of the reflector. It has been hypothized that diseased livers have physical structures which may scatter and attenuate ultrasound energy in different manner than healthy tissue. Numerical tissue characterization methods have attempted to measure the attenuation down-shift separately from gross tissue structures and to avoid non-homogeneous regions of tissue (such as central portions of the liver). It is an object of the invention to provide a method which is particularly useful to display frequency shift information in conjuction with a display of the intensity of reflected ultrasound pulses. To achieve this object the method according to the invention is characterized in that it further comprises the steps of : producing a second signal which corresponds to the deviation on the instantaneous frequency of said echoes from a reference frequency; modulating the hue of each pixel with a first color when the second signal produced from the corresponding echo is greater than zero and with a second colour when the second signal produced from the corresponding echo is less than zero; and modulating the saturation of each pixel as a function of the absolute value of the second signal produced from the corresponding echo. It is a further object of the invention to provide an apparatus for performing the method. The apparatus according to the invention is characterized in that it further comprises : an FM detector for producing a second signal, which represents the deviation of the instantaneous frequency of the echoes f(x,y) from a reference frequency, f o ; and a colour modulator for modulating the color of each pixel with the corresponding values of the second signal so that the hue of that pixel assumes a first color when the sign of the second signal is positive and assumes a second complementary color when the sign of the second signal is negative and for modulating the saturation of that pixel as a function of the absolute value of the corresponding second signal. The invention may be understood more fully with reference to the attached drawings in which : Figure 1 is a simplified chromaticity diagram which illustrates the invention; Fig. 2 is an echo ultrasound system which incorporates the invention; and Fig. 3 are plots of RGB multiplier values. It is well known that pseudocolor enhances human perception of gray scales and enables an observer to quantify a single parameter image. However, it is also known that most medical radiologists do not like pseudocolor images. Electronic Picture Archiving and Communication Systems (PACS) provide a convenient mechanism for storing multicolor images and ultrasound flow visualization systems now demonstrate the necessity for color displays when more than one independent parameter must be simultaneously displayed. It has been shown that color can allow the eye-brain combination to form useful correlations on multidimensional image data, if it can be used in a pleasing manner. It is known that separate use of red, green and blue to image three independent variables leads to confusing images. A more natural presentation is used in commercial color television and in map making where a primary image is shown as a high (spatial) resolution intensity image and secondary parameters are visualized by color tinting (which typically has less spatial resolution than the primary image). Thus, the hue (color) and the saturation (purity of color) can be used to present two independent low-resolution variables which are superimposed on a high resolution intensity image. Figure 1 schematically illustrates a two-dimensional chromaticity space of hue H and saturation S in polar coordinates. In the figure, S = 0 is white (zero color saturation) and the circle S = 1 represents pure monochromatic colors (fully saturated). On this circle the positions of the colours red (R), violet (V), blue (B) and yellow (Y) are shown. In this model, locations near S = 0 are pastel colors, such as pink (P) and sky blue (SB). In the prior art, three parameters of position in an image (such as a(x,y), f(x,y) and g(x,y)) were respectively assigned to Intensity, Hue and Saturation as, for example : where K i , K h and K s were constants. The simplest use of these relations is to set S = 0 everywhere (which implies that the hue is irrelevant) black and white intensity images are thus produced from the function a(x,y). In the usual prior art pseudocolor display, the single parameter, I(x,y) is set to a constant , S is set to unity (fully saturated color) and the parameter f(x,y) is imaged with hue as the only variable. Many people find such images distasteful. In a more acceptable prior art method, "color tinting" of a gray scale image is accomplished using all three equations. If only one additional parameter is of interest, it is common to set S equal to a constant and to use H(x,y) as the parametric variable. Thus color tinting of a black and white image conveys low resolution information as an overlay through which the observer can see the usual image of intensity information a(x,y) in the same manner as color tinted black and white photographs. If S is chosen as unity, this scheme is still unsatisfying to many observers. More pleasing images have been formed if S is set to a small value which leaves all colors as unsaturated pastels. In accordance with the present invention, the frequency deviation signal f(x,y) is used to tint an intensity image I(x,y) = a(x,y) with a combination of hue and saturation parameters so that the hue is determined by the sign of the deviation of the frequency from a reference value, f o , and the saturation is proportional to the absolute value of that deviation. For example : where C₁, f max , f min and f 0 are constants. Thus as f increases from its minimum to its maximum, the chromaticity follows a path, as illustrated by the broken arrow A in Figure 1, from a relatively saturated blue B through the pastel shades of blue SB through white (S = 0) and then through a pastel P and into a relatively saturated red color R. Any radial path inward from a saturated color to white and out again along another radial path to some contrasting color may be used. Figure 1 illustrates a path from blue through red. In a preferred embodiment, the path begins and ends at somewhat unsaturated pastel colors as this seems to provide a more pleasing image. The principle features of the image are : 1) when there is no deviation of the secondary parameter (the frequency) from its reference or equilibrium value, then the image is black and white without color tint; and 2) color deviations have a linear (one dimensional) directional sense (for example : from blue to red) which may be associated mentally as left-right, up-down, hot-cold, good-bad, big-­ little, etc. instead of the sometimes disorienting "circular loop" which occurs when hue modulation alone is used. Figure 2 is a block diagram of an echo ultrasound imaging system which incorporates the present invention. A transmitter 10 generates radio frequency electrical pulses which are directed via a T-R switch 20 to an ultrasound transducer 30. The transducer 30 converts the electrical pulses into pulses of ultrasound energy which are directed into a body undergoing examination 40. Portions of the ultrasound energy emitted from the transducer 30 are reflected from structures in the body (indicated schematicalloy as 50) and are returned as echoes to the transducer 30. The transducer converts the echoes into electrical echo signals which are transmitted via the T-R switch 20 to a receiver 60 where they undergo amplification and signal processing in a conventional manner. The output signals from the receiver are conveyed to an AM detector 70 and to an FM detector 80. The AM detector 70 may be of the conventional type utilized in prior art pulse-echoe ultrasound systems and may include time gain compensation (TGC) circuitry. The transmitter 10 and receiver 60 operate under the influence of signals from a control circuit 90. The control circuit also causes the beam of ultrasound from the transducer 30 to oscillate in a plane to generate a conventional sector scan of the body. In a preferred embodiment the transducer 30 may be motor driven to steer the ultrasound beam. Alternatively, stepped or phased array techniques may be utilized to steer the beam. A sweep signal from the control circuitry 90 is connected to a color display unit 100, which may be an RGB CRT display. In a conventional manner, the sweep signal from the control circuitry 90 scans the electron beam on the face of the CRT so that its instantaneous position maps pixels on the face of the tube which correspond to the points in the body from which the corresponding echo signals (which produce the outputs from the AM detector 70 and the FM detector 80) originate. The output signals, a(x,y) from the AM detector 70 and f(x,y) from the FM detector 80, are digitized, respectively, in A to D converters 110a and 110b. The outputs from the A to D converters 110a and 110b are fed to the address inputs of three ROM memories 120, 130 and 140. The ROM memories 120, 130 and 140 respectively contain look-­ up tables which translate the combined signals produced by the outputs of the AM detector 70 and FM detector 80 into intensity values which are applied, via D to A converters 150a, 150b and 150c to modulate the intensity of the red, blue and green electron guns of the color CRT. In a preferred embodiment of the invention, the look-up tables in the ROM memories 120, 130 and 140 respectively generate a red signal, R(x,y), a blue signal B(x,y), and a green signal G(x,y) in accordance with the formulas I(x,y) = K i a(x,y) R(x,y) = P R (x,y) I(x,y) G(x,y) = P G (x,y) I(x,y) B(x,y) = P B (x,y) I(x,y) where the multipliers P R , P G and P B are all less then unity and are functions of f(x,y) determined according to the mapping illustrated by the straight lines in Figure 3. When P min differs from zero, maximum saturation is not obtained. When the output of the FM detector 80 indicates that the center frequency of the return echoes is equal to the nominal center frequency of the echo signal, f 0 , all three color guns are balanced to produce a nominally white pixel. In that case each one of the three multipliers P R , P G and P B is substantially equal to the "white" value P W . It is also possible to obtain a particularly pleasing modulation scheme by varing the value of P W , that is to say the value of the intensity (I = R+G+B) is in fact slightly modulated by f(x,y). In a preferred embodiment the invention was implemented on a Hewlett-Packard Model 9040 computer using a Recognition Concepts Trapix 5500 digital display system. Data was obtained from a 3 MHz 19 millimeter transducer operating in a Philips SDU 3000 ultrasound display system. The data was digitized to eight bits while scanning a "normal" human liver and kidney. Pleasing images were obtained with the parameters illustrated in Figure 3 set to P W = 0.5, P min = 0.12, F min = 2.25 HMz, and F max = 2.75 MHz.

Claims: 1. A method for displaying a diagnostic ultrasound image comprising the steps of : directing pulses of ultrasound energy into a body and detecting echoes of the energy which are reflected from structures within the body; producing a first signal which corresponds to the instantaneous amplitude of the detected echoes; producing an image in which each pixel maps the location of the point of origin of a corresponding echo within the body; modulating the intensity of each pixel with the first signal produced from the corresponding echo; characterized in that the method further comprises the steps of : producing a second signal which corresponds to the deviation on the instantaneous frequency of said echoes from a reference frequency; modulating the hue of each pixel with a first color when the second signal produced from the corresponding echo is greater than zero and with a second color when the second signal produced from the corresponding echo is less than zero; and modulating the saturation of each pixel as a function of the absolute value of the second signal produced from the corresponding echo. 2. A method as claimed in claim 1, characterized in that the first color is red and the second color is blue. 3. Ultrasound imaging apparatus comprising : a transducer arrangement associated with a transmiter for directing a beam of ultrasound energy into a region of a body and with a receiver for detecting echoes of the energy which are reflected from structures within the body; an AM detector from producing a first signal, a(x,y), which represents the instantaneous amplitude of the detected echoes; a color display unit; a control unit for scanning the beam with respect to the body and for controlling the disply unit so that it produces an image wherein the position of each pixel maps the point of origin of corresponding echoes in the body; and an intensity modulator for modulating the intensity of each pixel with corresponding values of the first signal; characterized in that the apparatus further comprises : an FM detector for producing a second signal, which represents the deviation of the instantaneous frequency of the echoes f(x,y) from a reference frequency, fo; and a colour modulator for modulating the color of each pixel with the corresponding values of the second signal so that the hue of that pixel assumes a first color when the sign of the second signal is positive and assumes a second complementary color when the sign of the second signal is negative and for modulating the saturation of that pixel as a function of the absolute value of the corresponding second signal. 4. An apparatus as claimed in claim 3, characterized in that the colour modulator is adapted to modulate the saturation, S(x,y), in accordance with the formulae : where C₁, fmin and fmax are constants

Inventors: MAYO, WILLIAM TAYLOR
Applicants: NORTH AMERICAN PHILIPS CORPORATION
Application year: 1986
Main classification: G01S7
IPC codes: A61B8, G01S15, G01R33, G09G5, G01S7