Difference Between DFT and DTFT
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Arxiv:1712.04732V2 [Math.NA] 17 Jan 2021 New Window Function, Runtimes for the SE Method Can Be Further Reduced
Fast Ewald summation for electrostatic potentials with arbitrary periodicity D. S. Shamshirgar,a) J. Bagge,b) and A.-K. Tornbergc) KTH Mathematics, Swedish e-Science Research Centre, 100 44 Stockholm, Sweden. A unified treatment for fast and spectrally accurate evaluation of electrostatic po- tentials subject to periodic boundary conditions in any or none of the three spatial dimensions is presented. Ewald decomposition is used to split the problem into a real- space and a Fourier-space part, and the FFT-based Spectral Ewald (SE) method is used to accelerate the computation of the latter. A key component in the unified treatment is an FFT-based solution technique for the free-space Poisson problem in three, two or one dimensions, depending on the number of non-periodic directions. The computational cost is furthermore reduced by employing an adaptive FFT for the doubly and singly periodic cases, allowing for different local upsampling factors. The SE method will always be most efficient for the triply periodic case as the cost of computing FFTs will then be the smallest, whereas the computational cost of the rest of the algorithm is essentially independent of periodicity. We show that the cost of removing periodic boundary conditions from one or two directions out of three will only moderately increase the total runtime. Our comparisons also show that the computational cost of the SE method in the free-space case is around four times that of the triply periodic case. The Gaussian window function previously used in the SE method, is here compared to a piecewise polynomial approximation of the Kaiser-Bessel window function. -
7 Image Processing: Discrete Images
7 Image Processing: Discrete Images In the previous chapter we explored linear, shift-invariant systems in the continuous two-dimensional domain. In practice, we deal with images that are both limited in extent and sampled at discrete points. The results developed so far have to be specialized, extended, and modified to be useful in this domain. Also, a few new aspects appear that must be treated carefully. The sampling theorem tells us under what circumstances a discrete set of samples can accurately represent a continuous image. We also learn what happens when the conditions for the application of this result are not met. This has significant implications for the design of imaging systems. Methods requiring transformation to the frequency domain have be- come popular, in part because of algorithms that permit the rapid compu- tation of the discrete Fourier transform. Care has to be taken, however, since these methods assume that the signal is periodic. We discuss how this requirement can be met and what happens when the assumption does not apply. 7.1 Finite Image Size In practice, images are always of finite size. Consider a rectangular image 7.1 Finite Image Size 145 of width W and height H. Then the integrals in the Fourier transform no longer need to be taken to infinity: H/2 W/2 F (u, v)= f(x, y)e−i(ux+vy) dx dy. −H/2 −W/2 Curiously, we do not need to know F (u, v) for all frequencies in order to reconstruct f(x, y). Knowing that f(x, y)=0for|x| >W/2 and |y| >H/2 provides a strong constraint. -
Fourier Analysis of Discrete-Time Signals
Fourier analysis of discrete-time signals (Lathi Chapt. 10 and these slides) Towards the discrete-time Fourier transform • How we will get there? • Periodic discrete-time signal representation by Discrete-time Fourier series • Extension to non-periodic DT signals using the “periodization trick” • Derivation of the Discrete Time Fourier Transform (DTFT) • Discrete Fourier Transform Discrete-time periodic signals • A periodic DT signal of period N0 is called N0-periodic signal f[n + kN0]=f[n] f[n] n N0 • For the frequency it is customary to use a different notation: the frequency of a DT sinusoid with period N0 is 2⇡ ⌦0 = N0 Fourier series representation of DT periodic signals • DT N0-periodic signals can be represented by DTFS with 2⇡ fundamental frequency ⌦ 0 = and its multiples N0 • The exponential DT exponential basis functions are 0k j⌦ k j2⌦ k jn⌦ k e ,e± 0 ,e± 0 ,...,e± 0 Discrete time 0k j! t j2! t jn! t e ,e± 0 ,e± 0 ,...,e± 0 Continuous time • Important difference with respect to the continuous case: only a finite number of exponentials are different! • This is because the DT exponential series is periodic of period 2⇡ j(⌦ 2⇡)k j⌦k e± ± = e± Increasing the frequency: continuous time • Consider a continuous time sinusoid with increasing frequency: the number of oscillations per unit time increases with frequency Increasing the frequency: discrete time • Discrete-time sinusoid s[n]=sin(⌦0n) • Changing the frequency by 2pi leaves the signal unchanged s[n]=sin((⌦0 +2⇡)n)=sin(⌦0n +2⇡n)=sin(⌦0n) • Thus when the frequency increases from zero, the number of oscillations per unit time increase until the frequency reaches pi, then decreases again towards the value that it had in zero. -
Fractional Calculus and Generalised Norms in Condition Monitoring of a Load Haul Dumper
Fractional calculus and generalised norms in condition monitoring of a load haul dumper Master’s thesis Juhani Nissilä 1975600 Department of Mathematical Sciences University of Oulu Autumn 2014 Contents Introduction 4 1 Classical analysis 6 1.1 Norms and function spaces . 6 1.2 Convergence of function sequences . 9 1.3 Complex analysis . 10 1.4 Important theorems of analysis . 11 1.5 Distributions . 12 1.6 Iterated differences and derivatives . 16 1.7 Iterated integrals . 18 2 Mathematical background for fractional calculus 20 2.1 Gamma function . 20 2.2 Fourier series . 23 2.2.1 Series in L1;loc and L2;loc . 23 2.2.2 Pointwise convergence . 24 2.3 Fourier transform . 26 2.3.1 Transform in S and L1 . 26 2.3.2 Transform in L2 ...................... 28 2.3.3 Transform in S0 ...................... 29 2.3.4 Properties . 31 2.4 Poisson summation formula and the sampling theorem . 34 2.5 Discrete Fourier transform . 36 2.6 Window functions . 37 3 Fractional calculus in time domain 39 3.1 Riemann-Liouville fractional integral and derivative . 39 3.2 Caputo fractional derivative . 45 3.3 Grünwald-Letnikov fractional derivative and integral . 46 3.4 Equivalences of definitions . 47 4 Fractional calculus in frequency domain 49 4.1 Fourier differintegrals . 49 4.2 Weyl differintegrals . 52 4.3 Equivalences of definitions . 53 4.4 Numerical algorithm . 56 5 Norms, means and other features of signals 60 5.1 Generalised lp norms and Hölder means . 60 5.2 Measurement index . 64 1 6 Condition monitoring of a load haul dumper front axle 65 6.1 Data acquisition and acceleration signals . -
Arxiv:1801.05832V2 [Cs.DS]
Efficient Computation of the 8-point DCT via Summation by Parts D. F. G. Coelho∗ R. J. Cintra† V. S. Dimitrov‡ Abstract This paper introduces a new fast algorithm for the 8-point discrete cosine transform (DCT) based on the summation-by-parts formula. The proposed method converts the DCT matrix into an alternative transformation matrix that can be decomposed into sparse matrices of low multiplicative complexity. The method is capable of scaled and exact DCT computation and its associated fast algorithm achieves the theoretical minimal multiplicative complexity for the 8-point DCT. Depending on the nature of the input signal simplifications can be introduced and the overall complexity of the proposed algorithm can be further reduced. Several types of input signal are analyzed: arbitrary, null mean, accumulated, and null mean/accumulated signal. The proposed tool has potential application in harmonic detection, image enhancement, and feature extraction, where input signal DC level is discarded and/or the signal is required to be integrated. Keywords DCT, Fast Algorithms, Image Processing 1 Introduction Discrete transforms play a central role in signal processing. Noteworthy methods include trigonometric transforms— such as the discrete Fourier transform (DFT) [1], discrete Hartley transform (DHT) [1], discrete cosine transform (DCT) [2], and discrete sine transform (DST) [2]—as well as the Haar and Walsh-Hadamard transforms [3]. Among these methods, the DCT has been applied in several practical contexts: noise reduction [4], watermarking methods [5], image/video compression techniques [2], and harmonic detection [2], to cite a few. In fact, when processing signals modeled as a stationary Markov-1 type random process, the DCT behaves as the asymptotic case of the optimal Karhunen–Lo`eve transform in terms of data decorrelation [2]. -
Comparison of FFT, DCT, DWT, WHT Compression Techniques on Electrocardiogram & Photoplethysmography Signals
Special Issue of International Journal of Computer Applications (0975 – 8887) International Conference on Computing, Communication and Sensor Network (CCSN) 2012 Comparison of FFT, DCT, DWT, WHT Compression Techniques on Electrocardiogram & Photoplethysmography Signals Anamitra Bardhan Roy Debasmita Dey Devmalya Banerjee Programmer Analyst Trainee, B.Tech. Student, Dept. of CSE, JIS Asst. Professor, Dept. of EIE Cognizant Technology Solution, College of Engineering College of Engineering, WB, India Kolkata, WB, India Kolkata, WB, India, Bidisha Mohanty B.Tech. Student, Dept. of ECE, JIS College of Engineering, WB, India. ABSTRACT media requires high security and authentication [1]. This Compression technique plays an important role indiagnosis, concept of telemedicine basically and foremost needs image prognosis and analysis of ischemic heart diseases.It is also compression as a vital part of image processing techniques to preferable for its fast data sending capability in the field of manage with the data capacity to transfer within a short and telemedicine.Various techniques have been proposed over stipulated time interval. The therapeutic remedies are derived years for compression. Among those Discrete Cosine from the minutiae’s of the biomedical signals shared Transformation(DCT), Discrete Wavelet worldwide through telelinking. This communication of Transformation(DWT), Fast Fourier Transformation(FFT) exchanging medical data through wireless media requires high andWalsh Hadamard Transformation(WHT) are mostly level of compression techniques to cope up with the restricted used.In this paper a comparative study of FFT, DCT, DWT, data transfer capacity and rate. Compression of signals and and WHT is proposed using ECG and PPG signal, images can cause distortion in them. As the medical signals whichshows a certain relation between them as discussed in and images contains and relays information required for previous papers[1]. -
Lecture 5. FFT and Divide and Conquer
CS711008Z Algorithm Design and Analysis Lecture 5. FFT and Divide and Conquer Dongbo Bu Institute of Computing Technology Chinese Academy of Sciences, Beijing, China . 1 / 57 Outline DFT: evaluate a polynomial at n special points; FFT: an efficient implementation of DFT; Applications of FFT: multiplying two polynomials (and multiplying two n-bits integers); time-frequency transform; solving partial differential equations; Appendix: relationship between continuous and discrete Fourier transforms. 2 / 57 DFT: Discrete Fourier Transform n−1 DFT evaluates a polynomial A(x) = a0 + a1x + ::: + an−1x 2 n−1 2π i at n distinct points 1; !; ! ; :::; ! , where ! = e n is the n-th complex root of unity. Thus, it transforms the complex vector a0; a1; :::; an−1 into k another complex vector y0; y1; :::; yn−1, where yk = A(w ), i.e., y0 = a0 + a1 + a2 ::: + an−1 1 2 n−1 y1 = a0 + a1! + a2! ::: + an−1! ::: ::: ::: :::::: n−1 2(n−1) (n−1)2 yn−1 = a0 + a1! + a2! ::: + an−1! Matrix form: 2 3 2 3 2 3 1 1 1 ::: 1 y0 a0 6 7 6 1 !1 !2 :::!n−1 7 6 7 6 y1 7 6 7 6 a1 7 6 7 = 6 1 !2 !4 :::!2(n−1)7 6 7 4 . 5 6 7 4 . 5 . 4::::::::::::::: 5 . 2 yn−1 1 !n−1 !2(n−1) :::!(n−1) an−1 . 3 / 57 FFT: a fast way to implement DFT [Cooley and Tukey, 1965] Direct matrix-vector multiplication requires O(n2) operations when using the Horner’s method, i.e., A(x) = a0 + x(a1 + x(a2 + ::: + xan−1)). -
EE290T: Advanced Reconstruction Methods for Magnetic Resonance Imaging
EE290T: Advanced Reconstruction Methods for Magnetic Resonance Imaging Martin Uecker Introduction Topics: I Image Reconstruction as Inverse Problem I Parallel Imaging I Non-Cartestian MRI I Subspace Methods I Model-based Reconstruction I Compressed Sensing Tentative Syllabus I 01: Jan 27 Introduction I 02: Feb 03 Parallel Imaging as Inverse Problem I 03: Feb 10 Iterative Reconstruction Algorithms I {: Feb 17 (holiday) I 04: Feb 24 Non-Cartesian MRI I 05: Mar 03 Nonlinear Inverse Reconstruction I 06: Mar 10 Reconstruction in k-space I 07: Mar 17 Reconstruction in k-space I {: Mar 24 (spring recess) I 08: Mar 31 Subspace methods I 09: Apr 07 Model-based Reconstruction I 10: Apr 14 Compressed Sensing I 11: Apr 21 Compressed Sensing I 12: Apr 28 TBA Today I Review I Non-Cartesian MRI I Non-uniform FFT I Project 2 Direct Image Reconstruction I Assumption: Signal is Fourier transform of the image: Z ~ s(t) = d~x ρ(~x)e−i2π~x·k(t) I Image reconstruction with inverse DFT ky kx ) ) sampling iDFT ~ R t ~ image k(t) = γ 0 dτ G(τ) k-space Requirements I Short readout (signal equation holds for short time spans only) I Sampling on a Cartesian grid ) Line-by-line scanning α echo radio measurement time: slice TR ≥ 2ms read 2D: N ≈ 256 ) seconds phase 3D: N ≈ 256 × 256 ) minutes TR ×N 2D MRI sequence Poisson Summation Formula Periodic summation of a signal f from discrete samples of its Fourier transform f^: 1 1 X X 1 l 2πi l t f (t + nP) = f^( )e P P P n=−∞ l=−∞ No aliasing ) Nyquist criterium l For MRI: P = FOV ) k-space samples are at k = FOV I Periodic -
Digital Signal Processing & Its Applications
SCHOOL OF BIO AND CHEMICAL ENGINEERING DEPARTMENT OF BIOMEDICAL ENGINEERING UNIT – I – Digital Signal Processing & Its Applications – SEC1324 1 INTRODUCTION TO DISCRETE TIME SIGNALS AND SYSTEMS A signal is a function of independent variables such as time, distance, position, temperature and pressure. A signal carries information, and the objective of signal processing is to extract useful information carried by the signal. Signal processing is concerned with the mathematical representation of the signal and the algorithmic operation carried out on it to extract the information present. For most purposes of description and analysis, a signal can be defined simply as a mathematical function, y where x is the independent variable . y = f (x) signal e.g.: y=sin(ωt) is a function of a variable in the time domain and is thus a time signal X(ω)=1/(-mω2+icω+k) is a frequency domain signal; An image I(x,y) is in the spatial domain Fig.1:Classification 2 at t=0, will have the same motions at all time. There is no place for uncertainty here. If we can uniquely specify the value of θ for all time, i.e., we know the underlying functional relationship between t andθ, the motion is deterministic or predictable. In other words, a signal that can be uniquely determined by a well defined process such as a mathematical expression or rule is called a deterministic signal. The opposite situation occurs if we know all the physics there is to know, but still cannot say what the signal will be at the next time instant-then the signal is random or probabilistic. -
Digital Signal Processing EEE,EE,CSE Analog Electronics
Module – I 1.1 WHAT IS A SIGNAL We are all immersed in a sea of signals. All of us from the smallest living unit, a cell, to the most complex living organism (humans) are all time receiving signals and are processing them. Survival of any living organism depends upon processing the signals appropriately. What is signal? To define this precisely is a difficult task. Anything which carries information is a signal. In this course we will learn some of the mathematical representations of the signals, which has been found very useful in making information processing systems. Examples of signals are human voice, chirping of birds, smoke signals, gestures (sign language), fragrances of the flowers. Many of our body functions are regulated by chemical signals, blind people use sense of touch. Bees communicate by their dancing pattern. Some examples of modern high speed signals are the voltage charger in a telephone wire, the electromagnetic field emanating from a transmitting antenna, variation of light intensity in an optical fiber. Thus we see that there is an almost endless variety of signals and a large number of ways in which signals are carried from on place to another place. In this course we will adopt the following definition for the signal: A signal is a real (or complex) valued function of one or more real variable(s).When the function depends on a single variable, the signal is said to be one dimensional. A speech signal, daily maximum temperature, annual rainfall at a place, are all examples of a one dimensional signal. -
Discrete Cosine Transform Over Finite Prime Fields
THE DISCRETE COSINE TRANSFORM OVER PRIME FINITE FIELDS M.M. Campello de Souza, H.M. de Oliveira, R.M Campello de Souza, M. M. Vasconcelos Federal University of Pernambuco - UFPE, Digital Signal Processing Group C.P. 7800, 50711-970, Recife - PE, Brazil E-mail: {hmo, marciam, ricardo}@ufpe.br, [email protected] Abstract - This paper examines finite field the FFFT have been found, not only in the fields trigonometry as a tool to construct of digital signal and image processing [3-5], but trigonometric digital transforms. In particular, also in different contexts such as error control by using properties of the k-cosine function coding and cryptography [6-7]. over GF(p), the Finite Field Discrete Cosine The Finite Field Hartley Transform, which is a Transform (FFDCT) is introduced. The digital version of the Discrete Hartley Transform, FFDCT pair in GF(p) is defined, having has been recently introduced [8]. Its applications blocklengths that are divisors of (p+1)/2. A include the design of digital multiplex systems, special case is the Mersenne FFDCT, defined multiple access systems and multilevel spread when p is a Mersenne prime. In this instance spectrum digital sequences [9-12]. blocklengths that are powers of two are Among the discrete transforms, the DCT is possible and radix-2 fast algorithms can be specially attractive for image processing, because used to compute the transform. it minimises the blocking artefact that results when the boundaries between subimages become Key-words: Finite Field Transforms, Mersenne visible. It is known that the information packing primes, DCT. ability of the DCT is superior to that of the DFT and other transforms. -
Review of Signal Processing Sampling and Reconstruction
Review of Signal Processing This contains a brief review of • Sampling and Reconstruction • Decimation and Interpolation and Resampling Sampling and Reconstruction • I give a review of important facts about 1D theory, the 2D theory is analogous and available in the textbook (AK Jain, Chapter 2, 4). • Some references – The review below is based on the book: Signals and Systems, by Oppenheim, Wilsky and Yoeng. – Also see an excellent tutorial on the web (for figures, examples, and many more details): http://ccrma.stanford.edu/∼jos/mdft/mdft.html – Perfect interpolation of discrete periodic signals is possible to do. See S. Schanze, Sinc interpolation of discrete periodic signals, IEEE Trans Signal Processing, June 1995. Available at: http://ieeexplore.ieee.org/iel4/78/8826/00388863.pdf?arnumber=388863 • Disclaimer: This is a first draft, may have errors and typos, please email me ([email protected]) if you find them. ∞ • R without limits denotes R−∞. Similarly for Pn. • Let fs is sampling frequency, let Ts = 1/fs is the sampling interval. • Know/revise the following 1. Definition of CTFT (Continuous time Fourier transform) 2. Definition of DTFT (Discrete time Fourier transform) 3. Definition of DFT (Discrete Fourier transform) 4. Fourier transform properties and know common signal and CTFT/DTFT/DFT pairs. 5. Nyquist’s theorem, concept of aliasing. • To sample a signal at frequency fs, without aliasing (i.e. to be able to perfectly reconstruct it), it should be bandlimited to fs/2. If not, apply an appropriate Low Pass Filter. • Some important FT pairs 1. Comb function: x(t)= Pn δ(t − nTs), then X(f)= fs Pk δ(f − kfs) sin(2πWt) 2.