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# Signal processing in the cochlea: the structure equations

*The Journal of Mathematical Neuroscience*
**volume 1**, Article number: 5 (2011)

## Abstract

### Background

Physical and physiological invariance laws, in particular time invariance and local symmetry, are at the outset of an abstract model. Harmonic analysis and Lie theory are the mathematical prerequisites for its deduction.

### Results

The main result is a linear system of partial differential equations (referred to as the structure equations) that describe the result of signal processing in the cochlea. It is formulated for phase and for the logarithm of the amplitude. The changes of these quantities are the essential physiological observables in the description of signal processing in the auditory pathway.

### Conclusions

The structure equations display in a quantitative way the subtle balance for processing information on the basis of phase versus amplitude. From a mathematical point of view, the linear system of equations is classified as an inhomogeneous \overline{\partial}-equation. In suitable variables the solutions can be represented as the superposition of a particular solution (determined by the system) and a holomorphic function (determined by the incoming signal). In this way, a global picture of signal processing in the cochlea emerges.

## 1 Background

At the outset of this work is the quest to understand signal processing in the cochlea.

### 1.1 Linearity and scaling

It has been known since 1992 that cochlear signal processing can be described by a wavelet transform (Daubechies 1992 [1], Yang, Wang and Shamma, 1992 [2]). There are two basic principles that lie at the core of this description: Linearity and scaling.

In the cochlea, an incoming acoustical signal f(t) in the form of a pressure fluctuation (*t* is the time variable) induces a movement u(x,t) of the basilar membrane at position *x* along the cochlea. At a fixed level of sound intensity, the relation between incoming signal and movement of the basilar membrane is surprisingly linear. However as a whole this process is highly compressive with respect to levels of sound - and thus cannot be linear.

In the present setting this is taken care of by a ‘quasilinear model’. This is a model that depends on parameters, for example, in the present situation the level of sound intensity. For fixed parameters the model is linear. It is interpreted as a linear approximation to the process at these fixed parameter values. Wavelets give rise to linear transformations. The description of signal processing in the cochlea by wavelet transformations, where the wavelets depend on parameters, is compatible with this approach.

Scaling has its origin in the approximate local scaling symmetry (Zweig 1976 [3], Siebert 1968 [4]) that was revealed in the first experiments (Békésy 1947 [5], Rhode 1971 [6]).

The scaling law can best be formulated with the basilar membrane transfer function \stackrel{\u02c6}{g}(x,\omega ). This is the transfer function that is defined from the response of the linear system to pure sounds. To an input signal

that is, to a pure sound of circular frequency *ω* there corresponds an output u(x,t) at the position *x* along the cochlea that on the basis of linearity has to be of the form

The basilar membrane transfer function is thus a complex valued function of *x* and \omega >0. Its modulus |\stackrel{\u02c6}{g}(x,\omega )| is a measure of amplification and its argument is the phase shift between input and output signals. The experiments of von Békésy [5] showed that the graphs of |\stackrel{\u02c6}{g}(x,\omega )| and |\stackrel{\u02c6}{g}(x,c\omega )| as functions of the variable *x* are translated against each other by a constant multiple of log*c*. By choosing an appropriate scale on the *x*-axis, the multiple can be taken to be 1. The scaling law is then expressed as

The scaling law will be extended - with some modifications - to include the argument of \stackrel{\u02c6}{g}.

Intimately connected to scaling is the concept of a tonotopic order. It is a central feature in the structure of the auditory pathway. Frequencies of the acoustic signal are associated to places, at first in the cochlea and in the following stages in the various neuronal nuclei. The assignment is monotone, it preserves the order of the frequencies. In the cochlea, to each position *x* along the cochlear duct a circular frequency \sigma =\xi (x) is assigned. The function *ξ* is the position-frequency map. Its inverse is called the tonotopic axis. At the stand of von Békésy’s results, the frequency associated to a position *x* along the cochlea is simply the best frequency (BF), that is the frequency *σ* at which |\stackrel{\u02c6}{g}(x,\omega )| attains its maximum. The refined concept takes care of the fact that the transfer function and with it the BF changes with the level of sound intensity, at which \stackrel{\u02c6}{g} is determined. The characteristic frequency (CF) is then the low level limit of the best frequency. The position-frequency map *ξ* assigns to the position *x* its CF.

Scaling according to von Békésy’s results implies the exponential law

for the position-frequency map. The constant *K* is determined by inserting a special value for *x*. The scaling law tells us that the function |\stackrel{\u02c6}{g}(x,\omega )| is actually a function of the ‘scaling variable’

At the outset of the present investigation it will be assumed that the transfer function \stackrel{\u02c6}{g} is a function of the scaling variable \frac{\omega}{\xi (x)}. This is not strictly true, but it simplifies the exposition. In subsequent sections a general theory will be developed that incorporates quite general scaling behavior. With the availability of advanced experimental data (Rhode 1971 [6], Kiang and Moxon 1974 [7], Liberman 1978 [8], 1982 [9], Eldredge *et al.* 1981 [10], Greenwood 1990 [11]), the position-frequency map is now known precisely for many species. Shera 2007 [12] gives the formula

The constant *l* and the ‘transition frequency’ {\mathit{CF}}_{1} vary from species to species. The scaling variable that goes with it is

In the present setting, *x* is the normalized variable (*x* instead of x/l) and the precise position-frequency map is expressed in the form

*ξ* denotes circular frequency and K=\xi (0)+S. The constant *S* is referred to as the shift.

In the abstract model as it will be developed, much will depend on the definition of the function *σ* that specifies the frequency location. In the present treatment the frequency localization of a function will be defined as an expectation value in the frequency domain.

### 1.2 Wavelets

The response to a general signal f(t) with Fourier representation

is given as

Note that the Fourier transform of the real valued signal *f* satisfies \stackrel{\u02c6}{f}(\omega )=\overline{\stackrel{\u02c6}{f}(-\omega )}. If the definition of \stackrel{\u02c6}{g} is extended to negative values of *ω* by \stackrel{\u02c6}{g}(x,-\omega )=\overline{\stackrel{\u02c6}{g}(x,\omega )} then u(x,t) can be written as

The transfer function will be described by a function *h* in the scaling variable:

The response of the cochlea to a general signal *f* can then be expressed as

Setting a=\frac{1}{\xi (x)}=\frac{1}{K}{e}^{x} and thus x=k+loga with k=logK, the scaling function is simply h(a\omega ). This leads to the equivalent formulation

This is recognized as a wavelet transform. Indeed, with the standard {L}^{2}-normalization a wavelet transform *Wf* with wavelet *ψ* is defined by

If \frac{1}{\sqrt{2\pi}}h(\omega ) is identified with \overline{\psi (\omega )} then

The fact, that the cochlea - in a first approximation - performs a wavelet transform appears in the literature in 1992, both in [1] and in [2].

### 1.3 Uncertainty principle

The natural symmetry group for signal processing in the cochlea is built on the affine group Γ. It derives from the scaling symmetry in combination with time-invariance. In addition, there is the circle group *S* that is related to phase shifts. Its action commutes with the action of the affine group. The full symmetry group for hearing is thus \Gamma \times S. For this group, the uncertainty principle can be formulated. The functions for which equality holds in the uncertainty inequalities are called the extremal functions. They play a special role, similar as in quantum physics the coherent states (the extremals for the Heisenberg uncertainty principle). The starting point in the present work is the tenet that these functions provide an approximation for the cochlear transfer function.

That the extremal functions should play a special role is not a new idea. In signal processing the extremal functions first appeared in Gabor’s work (1946) [13] in connection with the Heisenberg uncertainty principle and then in Cohen’s paper (1993) [14] in the context of the affine group. In a paper by Irino 1995 [15] the idea is taken up in connection with signal processing in the cochlea. It is further developed by Irino and Patterson [16] in 1997. The presentation in this paper is based on previous work (Reimann, 2009 [17]). The concept pursued is to determine the extremals in the space of real valued signals and to use a setup in the frequency domain, not in the time domain. Different representations of the affine group give different families {E}_{c} of extremal functions. The parameter *c* is used to adjust to the sound level and hence to provide linear approximations at different levels to the non-linear behavior of cochlear signal processing.

## 2 Results and discussion

### 2.1 Uncertainty principle

This section starts with the specification of the symmetry group \Gamma \times S that underlies the hearing process. The basic uncertainty inequalities for this group are then explicitly derived. The analysis builds on previous results (Reimann [17]). A modification is necessary because the treatment of the phase in [17] was not satisfactory. An improvement can be achieved with the inclusion of the term \alpha \stackrel{\u02c6}{H} in the uncertainty inequality. This term comes in naturally and it will influence the argument - but not the modulus - of the extremal functions associated to the uncertainty inequalities. It is claimed that the extremal functions derived in this section are a first approximation to the basilar membrane transfer function \stackrel{\u02c6}{g}. The extremal functions for the basic uncertainty principle are interpreted as the transfer function at high levels of sound. This situation corresponds to the parameter value c=1. With increasing parameter values the extremal functions for the general uncertainty inequality are then taken as approximations to the cochlear response at decreasing levels of sound.

#### 2.1.1 The symmetry group

The affine group Γ is the group of affine transformations of the real line **R**. It is generated by the transformation group {\tau}_{b}(t)=t+b (b\in \mathbf{R}) and the dilation group {\delta}_{a}(t)=at (a\in \mathbf{R}, A\ne 0). Under the Fourier transform, the action of the dilation group on {L}^{2}(\mathbf{R},\mathbf{C}) is intertwined to the action of the inverse dilation group \stackrel{\u02c6}{\delta}. This group also acts directly in frequency space:

The induced unitary action on {L}^{2}(\mathbf{R},\mathbf{C}) is

(With this convention, the group action and the induced action are denoted with the same symbol.) Clearly, the invariance property of the basilar membrane transfer function directly reflects this group action.

The action

of the translation group intertwines under the Fourier transform to the unitary action

Of relevance to our considerations is the space {L}^{2}(\mathbf{R},\mathbf{R}) of real valued signals of finite energy. Under the Fourier transform it is mapped onto

Both \stackrel{\u02c6}{\delta} and \stackrel{\u02c6}{{\tau}_{b}} act on {L}_{\mathit{sym}}^{2}. The only action that commutes with both of them is the action

of the circle group S. This is the third distinguished group action.

The infinitesimal operators associated with the unitary actions of \stackrel{\u02c6}{\delta}, \stackrel{\u02c6}{{\tau}_{b}} and \stackrel{\u02c6}{\epsilon} are the skew hermitian operators

The commutator relations are

The operators \stackrel{\u02c6}{A}, \stackrel{\u02c6}{B} and \stackrel{\u02c6}{H} span the Lie algebra of the ‘hearing group’ \Gamma \times S, with Γ the affine group and S the circle group. The basic variables in cochlear signal processing are time *t* and position *x* along the cochlea. Clearly \stackrel{\u02c6}{B} is related to time, whereas \stackrel{\u02c6}{A} - as will be shown presently - is related to the position. In our approach the tonotopic axis is given by the exponential law

Under the tonotopic axis dilations {\stackrel{\u02c6}{\delta}}_{a} are conjugated to translations (by log*a*) in *x*:

Here, {\xi}^{-1}(\omega )=-log\frac{\omega}{K} is the inverse function with respect to the composition law. The intertwining action

is an isometry in the sense that for all h\in {L}^{2}(\mathbf{R},\mathbf{C})

It intertwines \stackrel{\u02c6}{A} with -\frac{d}{dx}:

as the following calculation shows:

The uncertainty principle that goes with the group \Gamma \times S can thus been seen as an uncertainty for the determination of time and position.

#### 2.1.2 The basic uncertainty inequality

The commutator relation

is at the basis of the uncertainty principle for the affine group. From the inequality

that has to hold for all \kappa \in \mathbf{R}, it follows that

In this calculation, the operators \stackrel{\u02c6}{A} and \stackrel{\u02c6}{B} can be replaced by \stackrel{\u02c6}{A}-\alpha \stackrel{\u02c6}{H}-\beta \stackrel{\u02c6}{B} and \stackrel{\u02c6}{B}-\nu \stackrel{\u02c6}{H} respectively. This leads to the new inequality

This inequality is of the same nature as the previous inequality. It can be considered as a more precise inequality, because it holds for all parameter values of *α*, *β* and *ν*. The expression \parallel (\stackrel{\u02c6}{H}\stackrel{\u02c6}{B}+\nu )h\parallel is minimal for

This *ν* is the decisive parameter. It has the interpretation of an expectation value for the frequency. Later it will be associated with the place along the cochlea.

The uncertainty inequality can thus be stated as

The minimality condition for the parameters *α* and *β* in the expression

is given by the linear system

The coefficients are

In this calculation, the fact that

has been used.

The remaining coefficient is

With h=\stackrel{\u02c6}{f} a different meaning can be given to it:

The integrals {\int}_{-\infty}^{\infty}{|h|}^{2}|\omega |\frac{d}{d\omega}argh\phantom{\rule{0.2em}{0ex}}d\omega and {\int}_{-\infty}^{\infty}t{|\frac{df}{dt}(t)|}^{2}\phantom{\rule{0.2em}{0ex}}dt can be interpreted as expectation values of {|h|}^{2}\frac{d}{d\omega}argh in the frequency space and for {|\frac{df}{dt}(t)|}^{2} in the time space. Roughly, in combination with \stackrel{\u02c6}{H} the operator \stackrel{\u02c6}{A} controls \frac{d}{d\omega}argh and \stackrel{\u02c6}{B} the time derivative.

We will assume that the parameters *α*, *β* and *ν* are always chosen such that the right hand side in the uncertainty inequality is minimal, that is, the inequality is formulated in its sharpest form.

The mean deviation from the expectation value *ν* for the modulus of the frequency is

The factor

does not have such a simple interpretation except in the special case \alpha =0. This is treated in [17].

A function *h* is called extremal, if equality holds for it in the uncertainty relation. The extremal functions are expected to play a special role in the signal processing of the cochlea. In the context of the classical Heisenberg uncertainty relation, the extremal functions are translates of the Gaussian function {e}^{-{x}^{2}} under the action of the Heisenberg group. They are called ‘coherent states’. Their significance in signal processing is well established since the appearance of Gabor’s work in 1946 [13]. At the outset of the present discussion is however the fact that the cochlea performs a wavelet transform - and not a Fourier transform. The invariance group is \Gamma \times S and not the Heisenberg group. It should therefore be expected that the extremal functions as discussed below play the crucial role in the hearing process.

The extremal functions *h* (in frequency space) satisfy the equation

This is in fact a differential equation:

The solutions are

with real constants *k*, *ε*, *α*, *β*, *κ* and *ν*. Square integrability implies \kappa >0 and *ν* is the positive frequency expectation value.

From the explicit form it is clear that the space of solutions is invariant under the action of \Gamma \times S. The tenet is now:

### 2.2 The basilar membrane transfer function is given by extremal functions

To be more precise, there exist an extremal function *h*, normalized by the condition \nu (h)=1, such that h(\frac{\omega}{\xi}) adequately describes the basilar membrane transfer function \stackrel{\u02c6}{g}:

In this formula, \xi =\xi (x) is the position-frequency map. Note further that

such that

The frequency expectation of \stackrel{\u02c6}{g}(x,\omega ) at *x* is thus \xi (x). The question then arises whether the experiments confirm the tenet. To arrive at a preliminary conclusion, graphs of the modulus and of the real part of the function *h* are displayed in Figure 1. The parameters are \alpha =-\pi, \beta =2\pi and \kappa =4.

The classical results by von Békésy (1947) [5] seem to be in favor of such a statement. However the situation is of course not so simple. The basic problem is the non-linearity of the process that associates the movement u(x,t) of the basilar membrane to the input signal f(t). This process is highly compressive and therefore its description by a transfer function can at best be looked at as an approximation.

Von Békésy’s result stem from experiments on dead animals. The outcome can be compared to the experimental results obtained with life animals, yet at high intensities of sound pressure. The above description of the basilar membrane transfer function is therefore taken to be a linear approximation at high levels of sound pressure. In the following section the approach will be modified with the aim of obtaining linear approximations at all levels of sound pressure.

#### 2.2.1 General uncertainty inequality for \Gamma \times S

There are various ways that the abstract group \Gamma \times S can act on the space {L}_{\mathit{sym}}^{2}. Apart from the natural representation that associates to the corresponding basis elements in the Lie algebra of Γ the operators \stackrel{\u02c6}{A} and \stackrel{\u02c6}{B}, the general representation considered below is built on the operators \frac{1}{c}\stackrel{\u02c6}{A} and {\stackrel{\u02c6}{B}}_{c}=-i{|\omega |}^{c}sgn(\omega ). The representation of Γ induced by this algebra representation retains the crucial scaling behavior known from the experimental results. It seems to be suitable in the present context, despite the fact that the operator {\stackrel{\u02c6}{B}}_{c} does not stand for the time derivative any more.

The general representation of \Gamma \times S on the space {L}_{\mathit{sym}}^{2} that will be considered is determined by the representation of its Lie algebra and as such by the operators \frac{1}{c}\stackrel{\u02c6}{A}, {\stackrel{\u02c6}{B}}_{c}=-i{|\omega |}^{c}sgn(\omega ) and \stackrel{\u02c6}{H}. There is the single non trivial commutator relation:

The uncertainty inequality that goes with it is

At this point it is not clear whether the term \frac{1}{c}(\stackrel{\u02c6}{A}-\alpha \stackrel{\u02c6}{H}-\beta \stackrel{\u02c6}{B}) should rather be \frac{1}{c}(\stackrel{\u02c6}{A}-\alpha \stackrel{\u02c6}{H}-\beta {\stackrel{\u02c6}{B}}_{c}). In fact the inequality is true for both variants and in both cases, families of inequalities depending on the parameters are obtained. The question is how the extremal functions that are associated to these inequalities vary with the parameters. Yet by choosing the present version one finds that the set of extremal functions is invariant under the action of \Gamma \times S. The expression \alpha \stackrel{\u02c6}{H}+\beta \stackrel{\u02c6}{B} should been seen as the linear approximation of the skew hermitian operator \stackrel{\u02c6}{A}. As a result of using both {\stackrel{\u02c6}{B}}_{c} and \stackrel{\u02c6}{B}, the first as an operator and the latter as an approximation term, this has the effect, that the argument of the extremal function appears in a slightly different context than the modulus. The extremal functions are obtained from the relation

They satisfy the differential equation

The proportionality factor is \kappa =-\frac{c\mu}{\lambda}. Its choice is arbitrary. All the constants *α*, *β*, and *κ* can in fact be chosen in dependence of the parameter *c*. This gives a possibility for fine adjustment of the extremal function {h}_{c} that describes the linear approximation at level *c* of the basilar membrane filter.

The solutions of the equation are

with real constants *k*, *ε*, *α*, *β*, *κ* and *ν*. These solutions are in {L}^{2} if both \kappa >0 and \nu >0.

The parameter in the uncertainty inequality is

This time, the frequency localization of the function *h* is

and

In accordance with our tenet, the basilar membrane filter is described as

with an extremal function {h}_{c}, normalized by the condition \nu ({h}_{c})=1.

As before, \xi =\xi (x) is the tonotopic axis. The frequency localization of \stackrel{\u02c6}{g}(x,\omega ) as a function of *ω* is *ξ*:

The parameter *c* allows to express at which level of sound intensity the linearization is specified. Parameters c\sim 1 indicate high levels and parameters c\gg 1 small levels of intensity.

Experimental results on the basilar membrane transfer function are reviewed in Robles and Rugggero, 2001 [18]. As already pointed out in the previous paper 2009 [17], the shape of the modulus of the transfer function determined at various intensities as given by Rhode and Recio (2000 [19], Figure 1C) is approximately described by the modulus of the extremal functions at the corresponding parameter values. In particular, at a fixed position, the modulus of the transfer function has its peak below the position of the frequency localization and with decreasing intensity of sound level it approaches this position. Similarly, for fixed *x*, the extremal functions |{\stackrel{\u02c6}{g}}_{c}(x,\omega )| attain their maxima at

With increasing values of *c* this approaches the frequency localization \xi (x).

With the present setup the argument of the basilar membrane filter is independent of *c*. The experimental results by Rhode and Recio (2000) show minor changes of phase in dependence of the intensity level. With increasing intensity there is a small phase lag below the characteristic frequency and an equally small phase lead for frequencies above the characteristic frequency. Studies of the impulse response also confirm that the phase is almost invariant under changes in sound level (Recio and Rhode (2000) [20], Shera (2001) [21]). In order to obtain a fine adjustment of the phase data, the parameters *α* and *β* would have to be chosen in dependence of *c*.

In any case, the phase function has to be a decreasing function both when considered as a function of the frequency *ω* and as a function of the place *x*. The phase of the extremal function does not satisfy this requirement because of the logarithmic term. Yet still, the phase of the extremal function serves as an approximation of the physiological phase function on the interval in which the the absolute value is relevant. At places at which the absolute value is close to zero, the argument is of no significance. In Figure 2 the phase function is pictured for the fixed circular frequency \omega =1\text{,}000 as a function of the distance *d* to the stapes, on the interval that is of physiological relevance. In Figure 3 the phase is pictured as a function of frequency (in Hz). In this figure, the characteristic frequency is 7,000 Hz. The part above about 3,000 Hz is of physiological relevance. The approximation holds in this range. It should be compared with the experimental results by Rhode and Recio (2000 [19], Figure 2E). The part below 3,000 Hz is the mathematical expression for the phase function. It is physiologically not correct, but this is of no significance.

The factor {e}^{-i\beta \omega} in the extremal functions {h}_{c} stands for a pure time delay by *β*. Dividing the extremal functions by this factor, one is left with the extremal functions as they would appear if *β* had been set equal to zero in the general uncertainty inequality. They are the extremal functions for the uncertainty inequality

### 2.3 The structure equations

Extremals for the uncertainty principle satisfy differential equations. Since the membrane transfer function is described by an extremal function and its transforms under the symmetry group and since the extremal functions are preserved under this action, it is possible to derive differential equations for the output of the signal. The resulting equations are called the structure equations.

The derivation starts with the simple case c=1. In this situation differentiation of the wavelet transform Wf(a,t) with respect to the parameters of the symmetry group directly leads to a differential equation. In the case c>0 however, the resulting equation is actually a pseudo differential equation. A linearization process for the kernel brings it back to a differential equation that is then satisfied approximately.

The quantities in the equation at first are derivatives of the output function Wf(a,t) and its Hilbert transform. A further calculation then shows that the result can be formulated as an inhomogeneous system of linear partial differential equations for the phase and for the logarithm of the amplitude of the output signal. This is particularly satisfying because these are exactly the physiologically relevant quantities.

The point of departure is the tenet that the basilar membrane transfer function is given as

with an extremal function {h}_{c} (normalized by the condition \nu ({h}_{c})=1).

As mentioned in the section ‘background’ the response to a general signal is interpreted as a wavelet transform:

with

The parameter in the wavelet transform can be normalized such that a=\frac{1}{\xi (x)}. The wavelet transform is then

The considerations in this section start from the formula

First the case c=1 is treated. It leads to exact results whereas in the case c>1 an approximation procedure will be applied.

Differentiation with respect to the variable *a* gives

Note that \stackrel{\u02c6}{A} commutes with {\stackrel{\u02c6}{\delta}}_{a}. The normalized extremal function *h* satisfies the differential equation

It follows that

Under the Fourier transform, -\frac{d}{dt} is mapped into \stackrel{\u02c6}{B} and the Hilbert transform *H* is mapped into \stackrel{\u02c6}{H}. This gives the basic equation

It is quite remarkable that the differentiation a\frac{\partial}{\partial a} (this essentially is differentiation with respect to *x*) brings in the Hilbert transform *H*. This transform is a unitary operator on {L}^{2}(\mathbf{R},\mathbf{C}). Its square is the negative of the identity operator: {H}^{2}=-I. It extends to a bigger class of functions (to all temperate distributions). On the basic trigonometric functions it operates very simply:

Experimentally, the basilar membrane function is - at least in many studies - determined in terms of the input signals cos(\omega t). It immediately follows that

holds for the functions f=cos(\omega t). The linearity assumption then implies that this holds for arbitrary input signals *f*.

Since \stackrel{\u02c6}{H} commutes with both \stackrel{\u02c6}{A} and \stackrel{\u02c6}{B}, the basic equation tells us that

The Hilbert transform thus appears naturally in this setting. This is the justification to study the ‘analytic wavelet transform’. Taking the factor \sqrt{a} into account this is

The complex valued function *Zf* then satisfies

Notice the shift by \frac{1}{2} that has its origin in the factor \frac{1}{\sqrt{a}}.

The basic equation can now be reformulated as a system of equations in the polar coordinates

The calculation in real terms starts with the observation that on one hand

whereas on the on the other hand

This gives the first equation

Similarly, on one hand

On the other hand

This gives the second equation

The calculation in complex notation makes use of the fact that

The basic equation is then

Dividing by *Zf* it follows immediately that

The case c\ne 1 is now being treated in a similar spirit. Recall that the normalized extremal functions (\nu =1) satisfy the differential equation

and that the basic equation derives from

The case c\ne 1 will not directly lead to a differential operator, because the operator {\stackrel{\u02c6}{B}}_{c} is not the Fourier transform of a differential operator (unless *c* is an odd natural number). It is however possible to use a linear approximation for {\stackrel{\u02c6}{B}}_{c} near the frequency expectation value of {h}_{c}, that is, at the point \omega =1:

The above equation is then approximated by

With the consequence that

The calculation for the analytic wavelet transform Zf=u+iHu then proceeds as above. Only the constants are slightly different. In the sequel the notation \gamma =c\kappa will be used. Recall that in prospective refined adjustments the parameters *α*, *β* and *γ* may vary with *c*.

The structure equations are

They combine to the complex equation

Equality holds if c=1.

Under the tonotopic axis \xi (x)=K{e}^{-x}, x=k+loga, the derivative a\frac{\partial}{\partial a} transforms into \frac{\partial}{\partial x}:

The structure equations can be written in x,t-coordinates:

### 2.4 Consequences of the structure equations

Signal processing in the cochlea is non-linear. The main - but certainly not the only - source of non-linearity is the compressive nature inherent in the hearing process. In the abstract model pursued here this is taken care of with a single parameter that represents the level of sound intensity. The model then describes the linear approximations at these levels. The structure equations are at the core of this abstract model, in fact they comprise all the essential features. First of all, they are linear (as would be expected from a linear approximation). From a mathematical point of view, the equations therefore are very simple. On top, the system is quite special. With respect to suitable variables it represents an inhomogeneous \overline{\partial}-equation. Its solutions can be realized in complex form as products of two factors, the first of which is entirely determined by the system and the second is a holomorphic function that can be calculated from the signal. At every level *c* it is thus possible to associate to an input signal in a unique way a holomorphic function that describes the output signal in terms of the physiological parameters.

The phase and the logarithm of the amplitude are used in the description of the experiments and they are omnipresent in all the representations of the auditory pathway. In themselves they are of limited significance, because they are not coded as such. What really is essential in any cochlear or in any neural model are the changes of these quantities, both with respect to time and with respect to the place. The structure equations precisely relate the local and temporal derivatives of phase and (logarithm of) amplitude. The geometry of the cochlea implicitly is inherent in the extremality property of the basilar membrane filter. But in the structure equations this only shows in terms of the constants. The implicit appearance of the tonotopic axis is an expression of the basic invariance principle that stands at the outset of all considerations.

The structure equations clearly exhibit the dichotomy in cochlear signal processing. The signals can either be analyzed in terms of their phase or in terms of their amplitudes. Assume that there is complete information on phase changes, that is, the quantities \frac{\partial \phi}{\partial t} and \frac{\partial \phi}{\partial a} are known. Then the second equation

can be solved for \frac{\partial}{\partial t}logr. Inserted in the first equation

this then determines \frac{\partial}{\partial a}logr. Conversely, the complete knowledge of amplitude information determines the phase information. From an abstract point of view, phase information and amplitude information each individually contain the full information of the signal. In the auditory pathway both phase and amplitude information is being processed. It is commonly assumed that phase information dominates in the low frequency range and amplitude information in the regions that process high frequencies. The equations tell us that phase processing and amplitude processing are equally significant.

The complex equation

shows that there is also a twofold way of data processing with respect to time and with respect to the place. Complete information on derivatives with respect to the position gives complete information on time derivatives - and *vice versa*.

The structure equations are so simple that they can be solved in explicit mathematical terms. In its complex form the structure equation is the linear inhomogeneous equation

The general solution of an inhomogeneous linear differential equation can be presented as the linear combination of a particular solution (any chosen solution of the equation) and the general solution of the associated homogeneous differential equation.

A particular solution log{Y}_{p} of the above complex equation is the function

Its distinguished feature is the time independence. It follows that the general solution log*Y* is of the form

for some function *X* satisfying the homogeneous equation

This leads to the product representation

(As a side remark, observe that the complex structure equation is obtained from the basic equation

after division by *Zf*. Writing

it is then clear that the homogeneous differential equation for *X* also holds at the zeros of *X*.) With the variable change

the homogeneous equation turns into a \overline{\partial}-equation for the transformed function

This then shows that the solutions of the linear inhomogeneous equation have the representation

with *G* a holomorphic function in the variable z=t-a\beta +ia\gamma. Since a>0 (and \gamma >0) it is defined in the upper half space \{z\in \mathbf{C}:Imz>0\}. The function G(z) is uniquely defined up to a constant.

The situation can now be summarized as follows: An incoming signal f(t) gives rise to a family of analytic wavelet transforms

depending on the parameter \gamma =c\kappa. The functions *Zf* approximately satisfy the complex structure equation. The solutions

of the equation

are then expected to provide approximations for *Zf* (with equality for c=1).

The functions *G* are holomorphic and depend on the parameter *γ*. They can in fact be determined directly from the Fourier transform of the incoming signal f(t). Since the system is linear, the superposition principle holds:

If f={f}_{1}+{f}_{2} is the superposition of two incoming signals {f}_{1} and {f}_{2} to which the holomorphic functions {G}_{1}(z) and {G}_{2}(z) are associated, then the holomorphic function for *f* is

All that has to be done is to calculate the holomorphic functions that correspond to to the basic functions f(t)=Acos(\nu t+\vartheta ). In the following section these are identified as the functions

The Fourier representation

then tells us that the holomorphic function associated to *f* is

The conclusion is that the holomorphic functions G(z) with z=t-a\beta +ia\gamma provide approximate solutions to the structure equation

The relevant expressions in the structure equations can then be calculated from the derivative of F(z):=logG(z):

### 2.5 Examples

#### 2.5.1 Pure sounds

For the input signal

the quantities logr(a,t) and \phi (a,t) can be calculated explicitly from the formula

This is

and for the derivatives

The first structure equation gives

This is in fact the correct linear approximation. It is equivalent with the linear approximation of {|a\nu |}^{c} at a\nu =1:

The second structure equation is satisfied as an equality.

From the complex structure equation the holomorphic function associated to f(t)=cos\nu t can be determined:

With the above approximation this is

(with the abbreviation c\kappa =\gamma). Observe that for c>1

unless a\nu =1. The approximate value for log|Zf| therefore is an over estimation. Together with

the result leads to

as the approximate value of logZf.

The associated holomorphic function is thus

with

Note that the holomorphic function *G* associated to the input signal

is

The constants *k* and *ε* are of little importance and do not show in the structure equations. In the following calculations we set k{e}^{i\epsilon}=1.

#### 2.5.2 Amplitude modulation

The amplitude modulated signal

with 0<\mu \ll \nu is described by the holomorphic function

The outcome depends on the ratio between the amplitudes of the coefficients. The frequency *ν* is dominant as long as

With

this gives the estimates

The frequency interval covered is

with

For sufficiently small values of *A* and \mu \ll \nu it includes the entire range along the cochlea that is involved in the processing of the amplitude modulated signal. The function *F* describing this signal in the relevant range can then be estimated by using the approximation log(1+x)\cong x for small |x|:

and

The result exhibits the basic frequency *ν* as the carrier frequency. But it should be warned that the approximation is valid only in the frequency interval specified above.

The relevant expressions in the structure equation can be calculated from {F}^{\prime}(z):

It can clearly be seen that there is the constant contribution from the carrier frequency and - as the interesting part - a slow oscillation of angular frequency *μ* that stems from sin(\mu z+\mathit{const}). Both the amplitude and the phase derivatives show this oscillation.

#### 2.5.3 The sound of a violin

No doubt, the distinguished feature of a violin sound is the extraordinary big number of harmonics in the frequency spectrum. It is not uncommon to observe around twenty harmonics at an intensity level at which the sounds can still be detected. Except possibly for the first few, the harmonics show a gradual decrease in amplitude with some oscillation. It is conjectured that these properties are in fact characteristic for violins of good quality. Figure 4 shows the amplitudes of the individual harmonics of the violin sounds *a*{e}^{\prime} and {d}^{\u2033}. The program ‘Prisma-Realtime’ by Bachmann *et al.* (2007) [22] uses windowed Fourier transform for this spectrogram. The amplitudes are determined at short intervals and marked with a point. The intensity of these points is fading with the time.

The violin sound has the representation

Figure 4 indicates that |{c}_{m}| decreases exponentially in *m*. In the dB-scale the decrease is roughly linear with slope −2:

(with the approximation 10\cong {e}^{2.3}).

The associated holomorphic function is

It is a Fourier series {\sum}_{m=1}^{\infty}{d}_{m}{e}^{im\nu t} with coefficients

depending on the position (represented by the variable *a*). The amplitudes

are maximal for

At the place along the cochlea that codes for the angular frequency *nν*, that is, for \xi (x)=\frac{1}{a}=n\nu, the coefficient {d}_{n} is thus dominant. In a neighborhood of this {n}^{\mathrm{th}} harmonic (near a=\frac{1}{n\nu}) the function *F* can be described locally. The calculation exhibits apart from the contribution by the carrier frequency a substantial oscillatory part of angular frequency *ν*. In a first calculation only the influence of the two closest harmonics is taken into account. The partial signal

corresponds to the function

As before, the approximation

is used. The coefficients

are decomposed as

with s={c}_{+}+{c}_{-} and d={c}_{+}-{c}_{-}. This gives the approximation

near the {n}^{\mathrm{th}} harmonic. The carrier frequency accounts for the part in\nu z+P(n\nu )+logA+i\theta. In the structure equation it only participates with time independent terms. But the significant part is the contribution that varies in time with angular frequency *ν* (recall that z=t-a\beta +ia\gamma).

The qualitative picture remains unchanged, if several neighboring harmonics are considered. Near the {n}^{\mathrm{th}} harmonic the dominant term in the function F(z) is expected to be in\nu z+P(n\nu )+log{c}_{n}.

This shows the presence of the carrier frequency. The remainder term is approximated by

This function is \frac{2\pi}{\nu}-periodic in time, with leading term

In conclusion it can be said that locally around a=\frac{1}{n\nu} the function F(z) is of the form

with a well defined remainder term that is \frac{2\pi}{\nu}-periodic in time. The term in\nu z+P(n\nu )+log{c}_{n} shows the presence of the carrier frequency. The relevant information about the violin sound is however contained in the fact that the \frac{2\pi}{\nu}-periodicity extends over an interval along the cochlea that comprises more than three octaves in the tonal range. The nature of this contribution is similar all along the interval covered by the frequency spectrum of the violin sound. The exceptions are the low harmonics (essentially the first and second) at which the influence of the neighboring harmonics is very small. Furthermore, the amplitude spectrum of a violin sound very often fails to display monotonicity for the first few harmonics.

With regard to the violins, it should be mentioned that there are considerable differences between different (good quality) instruments. It is believed that the distribution in the first few harmonics very much contributes to the individuality of the violin.

### 2.6 The impulse response

The response to the impulse function (the dirac function at the origin) is up to rescaling the inverse Fourier transform {\stackrel{\u02c7}{h}}_{c} of the extremal function

For simplicity it is assumed that k{e}^{i\epsilon sgn(\omega )}=1. Since the Fourier transform of the dirac function is the constant function \frac{1}{\sqrt{2\pi}}, the impulse response is

Therefore au(logK+loga,t)={\stackrel{\u02c7}{h}}_{c}(\frac{t}{a}) is a function of the single variable s=\frac{t}{a}. This could also be expressed by saying that tu(x,t) only depends on the single variable *s* - the usual way to formulate the invariance statement.

Figure 5 shows the impulse response for different values of *c*. The impulse response must have its support on the positive half of the time axis. The membrane cannot show a reaction before the impulse arrives. The numerical calculations show that this is almost satisfied. At this point attention should be drawn to a deficiency of the approach. The basic difficulty lies in the concept of using the uncertainty principle. The appropriate thing would be to restrict the class of functions in the uncertainty principle to functions that in the time domain are supported on the positive half axis. However, in the restricted class there are no extremal functions. This can be seen from the fact that the class of extremal functions is translation invariant in the time domain. With the present setting it is not strictly true that the impulse response has its support on the positive half axis. The extremal functions have to be interpreted as a first approximation. They have to be modified slightly such that they really vanish for negative values of *t*. The numerical calculations show that only small modifications are necessary.

The invariance property of the impulse response mentioned above in combination with the structure equations allow for an explicit approximate calculation of {\stackrel{\u02c7}{h}}_{c}. In the case c=1 this procedure gives the precise value up to a multiplicative constant.

Recall that

was the analytic response. The functions *f* and *g* are then defined starting from au(k+loga,t) as

The derivatives appearing in the structure equations can be expressed in terms of {f}^{\prime} and {g}^{\prime}:

They are inserted in the structure equations. The result is a system of differential equations for the functions {f}^{\prime} and {g}^{\prime} of the variable *s*.

or equivalently

The complex calculation is quickly done.

All that remains is to determine the integration constant *K*. The inverse Fourier transform {\stackrel{\u02c7}{h}}_{c} of {h}_{c} is then approximated as

This is an exact result if c=1.

The function log(s-\beta +i\gamma ) is well defined and holomorphic for Ims>-\gamma. In this range

can be chosen in the interval (0,\pi ). The modulus of the holomorphic function

is then bounded in the upper half plane. Therefore the function F(z) associated to the impulse response is holomorphic and can be calculated from it. Since *z* and *s* are related by z=t-a\beta +ia\gamma =a(s-\beta +i\gamma ), it follows that

Therefore

and this function is indeed holomorphic in the upper half plane.

The determination of the integration constant is left open. There is however some information that can be obtained directly from the differential equations for *f* and *g*. The above system is solved for {f}^{\prime} and {g}^{\prime}:

From the equation \frac{\partial}{\partial t}g(\frac{t}{a})=\frac{1}{a}{g}^{\prime}(\frac{t}{a}) an estimate for the peak of log*r* at the position given by the angular frequency \frac{1}{a} can be obtained. The peak is determined by {g}^{\prime}(s)=0:

This equation tells us how the peak arising from a click travels along the cochlea.

Information on the derivative of the phase is obtained from \frac{\partial}{\partial t}\phi (a,t)=\frac{1}{a}{f}^{\prime}(\frac{t}{a}). For this the second derivative of *f* is calculated:

Near the peak of log*r* the second derivative is small and it changes sign between \beta +\alpha and *β* (recall that \alpha <0):

Therefore {f}^{\prime} is a slightly increasing function at s=(\alpha +\beta ) and it is slightly decreasing at s=\beta. The function {f}^{\prime} itself takes values close to 1:

The graph of {f}^{\prime}(s) is shown in Figure 6. The parameter values are \alpha =-5.3\pi, \beta =16\pi, furthermore, \gamma =32\pi.

According to Shera [23] frequency glides in click responses of the basilar membrane have their origin in the dispersion properties of the slow traveling wave. The variable s=\frac{t}{a}=t\xi (x) is the scale invariant variable denoted by 2\pi \tau =t2\pi {f}_{\mathit{CF}}(x) in [23], p. 2025. Above, the frequency is expressed in the variable *s* as \phi (a,t)=f(s). This gives

for the instantaneous frequency and hence {f}^{\prime}(s)=\frac{1}{\xi (x)}\frac{\partial \phi}{\partial t}(a,t) for the normalized instantaneous frequency. In [23], p. 2025, Shera denotes it by {\beta}_{in}(\tau ) and pictures its graph in Figure 2b. The above calculations show that {f}^{\prime}(s) is increasing for values below \alpha +\beta. This can be interpreted as a frequency glide. Note that {f}^{\prime}(s) starts to decrease near *β*. Hence Figure 2b in [23] would roughly confirm the present calculations provided that \alpha +\beta \approx 12\pi. There is however a difference in that the present calculation exhibits a dependence of {f}^{\prime} on the sound level (as represented by *c*) with maximal values for {f}^{\prime} that are slightly bigger than one.

### 2.7 General invariance groups

Scale invariance as considered in the previous sections is based on the dilation group {\delta}_{a} and on the assumption that the tonotopic axis is given by the exponential law \xi (x)=K{e}^{-x}. From the experimental data it should however rather be concluded that the symmetry hypotheses are satisfied only locally and in a first approximation. The question therefore arises whether the results subsist qualitatively when these basic assumptions are modified. To answer this question the setup of an abstract model is being presented.

The basic hypothesis is still that the symmetry in cochlear mechanics is given by a one parameter transformation group {\stackrel{\u02c6}{\lambda}}_{a} acting in phase space. This action can be taken in a quite general form. Ideally it should be possible to adapt it individually to each species. The specific form of the tonotopic axis is to a certain extent independent of the action of the one parameter group. It will be discussed as a separate issue and for the time being the exponential law will be retained.

The transformation group {\stackrel{\u02c6}{\lambda}}_{a} thus stands at the outset of a general framework for an abstract description of cochlear mechanics. The one parameter group will be enlarged to a bigger group. At first this will be done on the infinitesimal level by defining a multiplier operator \stackrel{\u02c6}{M} that plays the role of \stackrel{\u02c6}{B}=-i\omega in the previous sections. Together with the infinitesimal generator \stackrel{\u02c6}{L} for the one parameter group {\stackrel{\u02c6}{\lambda}}_{a} and together with \stackrel{\u02c6}{H}, the action of the Lie algebra of the abstract symmetry group is then completely determined. As an abstract group, the symmetry group is still \Gamma \times S, yet the action in phase space will have changed. It will in fact be conjugate to the standard action. The conjugation mapping typically maps a bounded symmetric range in frequency space onto the whole frequency axis. In the application the bounded range will be the interval (-R,R). The upper bound *R* appears as an absolute frequency bound. In such a model, the inner ear is completely indifferent to signals whose frequency content lies beyond this limit.

As a first issue the wavelet transform for general one parameter groups is being discussed. Next the action of the one parameter group is determined in dependence of the parameter *c* that relates to the overall sound level of the signal. This action will then be extended on the infinitesimal level to all of \Gamma \times S. Along with this, the conjugation mapping will be defined.

#### 2.7.1 The wavelet transform for general one parameter groups

One parameter transformation groups on {\mathbf{R}}^{+}=(0,\infty ) are generated by vector fields v:{\mathbf{R}}^{+}\to \mathbf{R}. Assume that *v* extends to a continuous odd function on **R** and that the solutions {\tau}_{t}(\omega ) to the differential equation

with initial condition {\tau}_{0}(\omega )=\omega are uniquely determined and depend smoothly on the initial condition *ω*. Then {\tau}_{t} is a one parameter transformation group of {\mathbf{R}}^{+}. It extends in an antisymmetric way to all of **R**. At the point x=0 the vector field vanishes and x=0 is a stationary solution of the differential equation. Let us transform the time parameter *t* and set

The one parameter group \{{\lambda}_{a}\} is then written with a multiplicative parameter a\in {\mathbf{R}}^{+} (the multiplicative group of positive real numbers). It then follows that

Example

The differential equation has the solutions

Assume that the vector field *v* has a finite number of zeroes \pm {x}_{i}, labeled in ascending order

(the point {x}_{k}=\infty is included though this is not necessarily a zero of *v*). If

then {\lambda}_{a}\omega stays in {I}_{i} for all a\in {\mathbf{R}}^{\ast}. If in addition v>0 in {I}_{i}, then

and

The variable transform \zeta ={\lambda}_{a}\omega,

gives

whenever the integrals exist. If however v<0 in {I}_{i} then the sign changes. Hence in both cases

If {\tau}_{t}(\omega ) is the solution of the differential equation \frac{dx}{dt}=v(x) with initial condition {\tau}_{0}(\omega )=\omega then the variational equation is

Integrating with respect to *t* gives

This can be written as

The formula expresses that \frac{|d\omega |}{|v(\omega )|} is the invariant measure for the group action.

The transformation group \{{\lambda}_{a}\} induces a unitary representation *λ* on {L}^{2}(\mathbf{R},\mathbf{C}):

(The same notation {\lambda}_{a} is used for both the group and its unitary representation. To be consistent with the previous notation the group should actually be denoted by {\stackrel{\u02c6}{\lambda}}_{a}, since it will be taken as a group that acts in phase space.)

Note that

is a cocycle for the transformation group \{{\lambda}_{a}\}.

Given the transformation group \{{\lambda}_{a}\} in phase space and a function \psi \in {L}^{2}(\mathbf{R},\mathbf{C}), define the one parameter family of wavelets by

The wavelet transform with wavelet *ψ* and transformation group \{{\lambda}_{a}\} is

The isometry properties of the wavelet transform have their origin in the isometry property of the Fourier transform. Applied to {W}_{\psi} they give

This equality is integrated with respect to the measure \frac{da}{a} and the order of integration is interchanged:

With the change of variables \omega ={\lambda}_{a}(\sigma ) the integration with respect to \frac{da}{a} can be transformed into an integration over the interval {I}_{i}=({x}_{i},{x}_{i+1}) that contains *ω*:

Assume now that *ψ* is a real valued wavelet. Then

From the formula it can be concluded that the full information on *f* is contained in the wavelet transform, provided the integrals are finite and the constants {C}_{i} different from zero for all indices. A formal reconstruction can be obtained in terms of the wavelets

(Notice the negative sign in the exponent!)

The corresponding wavelet transform is

A similar calculation as before then gives

The function is thus recovered weakly in the sense of {L}^{2}-duality by

For the description of cochlear mechanics the reconstruction of the signal from its output at the cochlear level (that is, from its wavelet transform) is not an issue. No reconstruction is taking place in the auditory pathway. However from the point of information processing it is of relevance to know whether the wavelet transform contains the full information of the original signal.

In the application the wavelet transform will be described by a wavelet with frequency support in [-R,R]. The above reconstruction process would then give the projection of the signal onto the subspace of band limited signals.

#### 2.7.2 Extension of the group action

In the case of the dilation group when {\lambda}_{a} is {\stackrel{\u02c6}{\delta}}_{a} and the generating vector field is v(x)=-x, the operator \stackrel{\u02c6}{B}=-i\omega together with the infinitesimal generator \stackrel{\u02c6}{A}=\frac{1}{2}+\omega \frac{d}{d\omega} for the action of the dilation group satisfy the commutator relation

of the Lie algebra of the affine group Γ. For general vector fields *v*, the infinitesimal generator for the group action is

Together with \stackrel{\u02c6}{B} it will in general fail to span a finite dimensional Lie algebra of operators. However there exists a skew hermitian multiplier operator *M* such that

The multiplier of *M* can be taken in the form

The symmetric real valued function s(\omega ) is then determined by the differential equations that results by applying the commutator relation

In any interval void of zeros of the vector field, the function *s* is determined up to a multiplicative factor by

If *v* is a smooth vector field with zeros at \pm {x}_{i} then s(\omega ) will map any interval {I}_{i}=({x}_{i-1},{x}_{i}) onto the positive real half axis {\mathbf{R}}^{+}. Furthermore, it will conjugate the action of the transformation group {\lambda}_{a} (restricted to {I}_{i}) with the action of the dilation group {\stackrel{\u02c6}{\delta}}_{a}:

This can be verified by calculating the infinitesimal generator of the conjugate group:

The conjugation map *s* induces an isometry {s}^{\ast} between {L}^{2} and the subspace {L}_{I}^{2} of {L}^{2}-functions restricted to -{I}_{i}\cup {I}_{i}:

In the application, the interval on which {\lambda}_{a} acts will be I=(0,R) and the vector field will take negative values. The function sgn(\omega )s(\omega ) then maps (-R,R) onto **R** and conjugates {\lambda}_{a} to {\stackrel{\u02c6}{\delta}}_{a}.

The operators *L* and *M* satisfy the commutator relation of the Lie algebra of the affine group Γ. The action of the group {\lambda}_{a} is thus extended on the infinitesimal level to a Lie algebra action of the affine group.

It can be lifted to \Gamma =\{(a,t):a>0,t\in \mathbf{R}\} by setting

The circle group action {\stackrel{\u02c6}{\epsilon}}_{\phi} with infinitesimal generator \stackrel{\u02c6}{H} remains unchanged and commutes with the Γ-action

The operators corresponding to {\stackrel{\u02c6}{B}}_{c} are

The only non trivial commutator relation is

For later use note that {\lambda}_{a} commutes with *L*, whereas

#### 2.7.3 The uncertainty inequality

For a given vector field generating the transformation group {\lambda}_{a}, an interval {I}_{i}=({x}_{i-1},{x}_{i}) is fixed. The signal space {L}^{2}(\mathbf{R},\mathbf{R}) is then restricted to the subspace {L}_{I}^{2} of band limited signals with frequencies in $$