- Biomedical Research (2015) Volume 26, Issue 4

## Automated System for Ultrasound Hyperthermia Cancer Treatment based on POF Controller

**Jeraldin Auxillia D ^{*}**

St. Xavier’s Catholic College of Engineering, Chunkankadai,Nagercoil, Tamilnadu, India

- Corresponding Author:
- Jeraldin Auxillia D

St. Xavier’s Catholic College of Engineering Chunkankadai, Tamilnadu India

**Accepted date:** June 03 2015

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### Abstract

Hyperthermia, the heating of cancerous tumors can improve the efficiency of cancer treatment when added as an adjuvant to Radio therapy and Chemotherapy. Main goal of this work is to design a periodic output feedback controller to control the power of ultrasound transducer so that uniform temperature distribution is maintained in the targeted tissues all through the hyperthermia treatment process. For this purpose first a tumor layer surrounded by muscle layer is modeled using Penne’s bio heat transfer equation and a higher order state space model to the bio heat transfer problem is obtained by finite difference method. In second step an experimental proto type for the above model is created using agar phantom which mimics the human tissue. Temperature response of the simulated model is compared with the experimental outcome to demonstrate the validity of simulated model. Now a periodic output feedback controller is designed for the simulated hyperthermia model. The performance of the controller is evaluated by framing a desired trajectory which meets the treatment goals of hyperthermia. Closed loop error norm and the open loop error norm are evaluated to prove the efficiency of the designed controller. Simulations are also done to show the robustness of the controller in spite of variation in blood perfusion. Simulations proved that hyperthermia system is robust to blood perfusion variation and the closed loop norm has improved more than 40% compared to open loop norm in certain perfusion cases.

## Keywords

Hyperthermia, Blood perfusion, Periodic output feedback, Bio- heat transfer, ultrasound transducer.

## Introduction

Cancer is a major hazard to human life. Hyperthermia the heating of cancerous tumors, can improve response rates when added as an adjuvant treatment to radiation therapy. Recent experiments on human subjects confirm that in cervical cancer and recurrent lesions of malignant melanoma the response rate is 53% and 28% for patients who received radiation only and the response rate has improved to 83% and 46% respectively for patients who received radiation in adjuvant with hyperthermia. Reoxygenation of the hypoxic tumor regions occur and become radiosensitive, when tumor temperature is raised to 40°C - 44°C for 30-60 min .The prime goal of an online hyperthermia controller is to maintain desired temperature of 43°C within the tumor while limiting temperatures outside the tumor to safe levels of < 40 °C from a baseline body temperature of 37°C [1].This goal must be met under the influence of variable blood perfusions, that lead to plant model mismatch [2]. Several control algorithms have been suggested for this purpose.

Formerly many researchers have developed automatic temperature controllers for various hyperthermia systems such as scanned focused & phased array ultrasound. Many control ideas in the range of basic PID [3], LQR controller [4], multipoint adaptive, more complex model predictive [2], Constrained Predictive Control [5], Minimum- Time Thermal Dose Control [6] and even recursive control procedure [7] were used to design the system. Due to complexity of human body and finite difference modeling the full order models developed were too large. Potocki and Tharp [8], Mattingly and Romer [1] and Marshal et. al [9] reduced the order of the hyperthermia system and designed controllers. But none of the designed controllers relay on reduced models for designing controller for higher order system, Lamba and Rao [10] showed that if a state feedback control is designed from the Davison [11] reduced model and applied to the higher order system it results in stable closed loop system but this necessitates the system state to be available for feedback.

In hyperthermia, it is essential to retain a homogeneous temperature in the tissue and tumor. If the distribution of temperatures within the tumor shows considerable dispersion about it mean value, treatment failures and complications are liable to occur i.e cold spots never reach therapeutic temperatures and so are not treated. Similarly hot spots lead to complications such as unbearable pain and ulceration of the overlying skin. So to have uniform temperature distribution it is sensible to measure the temperature at each node. As in hyperthermia all system states are not accessible for feedback it insists the need for estimator design, this makes the system complex and reduces system reliability. Hence, it is rather attractive to go for an output feedback design. The output feedback needs only the measurement of system output in contrast, to the state feedback which requires the knowledge of the states or a state estimator. In such a situation it is better to use periodic output feedback technique which requires the feedback of the output temperature signal only. Comparison to other techniques periodic output feedback is much simpler. The control signal is kept constant over few measurements and altered periodically.

Although the existing controllers are capable of satisfying the basic needs of on line hyperthermia system they claim for the need of estimator and the reduced order controller does not guarantee the closed loop stability for the higher order system. So in the proposed method an output feedback controller is designed for higher order discrete system via reduced order model. The benefits of the method are two folds, first the states of the system need not be estimated and secondly when the controller is placed in the closed loop with the higher order it guarantees the closed loop stability. This study is a first effort towards including an output feedback controller for hyperthermia system.

## Materials

*Tumor & Ultrasonic Field Modeling*

A simple 1-D inhomogeneous tissue is modeled as a tumor
layer surrounded by muscle layer on either side as in **Figure
1**.

The bio heat transfer equation presents useful predictions to estimate the temperature distribution in hyperthermia .The thermal response of tissue is modeled using the Penne’s bio heat transfer equation [12].

(1)

Arterial temperature *T _{a}* is assumed to be 37°C and

*Q*is the power deposited in the ultrasonically heated tissue. The heterogeneous tissue with tumor modeled in 1-D using Penne’s bio heat equation contains conduction effects, geometrical information on normal and diseased tissue. The parameter W

_{a}_{b}characterizes the energy eliminated by conduction in the plane at right angles to the ultrasound axis.

**Table-1**summarize the thermal properties of human tissue.

Thermal conductivity is assumed to be constant and ‘x’ is
the depth of penetration inside the tissue. In our model x
varies from 0 to 13 cm and the boundary condition are
assumed to be *T (0, t) = Ta* and *T (L, t) = Ta*. This is due
to thermoregulation effect. In this paper we assume a single
scanned focused ultrasound transducer with fixed
characteristics .The power deposition term Q_{a} is modelled
as the energy deposited by scanned focused ultrasound
transducer and given

(2)

Where *Q _{i} (x), α_{i}* and

*S*are energy deposition, attenuation co-efficient and penetration length for layer ’r’ The transducer is positioned 17cm from the front edge of the tissue with r=25cm, d=70mm, l =1mm. Where I(0) is the average intensity over the radiating surface ‘d’ is the diameter of the transducer ’r’ is the radius of curvature and ‘x’ is the distance from the centre of the transducer

_{i}*State Space Formulation*

The numerical method finite difference is used for solving the partial difference equation of bio heat transfer.

(3)

Assume is the elevated temperature, where represents the temperature in the tissue and T_{a} arterial
temperature.

(4)

The tissue model is split into 131 finite difference nodes .The temperature distribution in each node is known based on equation (4) and power deposition in each node is given according to equation (2).

The system matrix A is a higher order tri-diagonal matrix
with non zero elements only on its main diagonal and upper
and lower diagonals. and symbolizes the tri-diagonal elements of normal tissue and signify the tri-diagonal elements of tumor tissue respectively.
Here c_{1}and c_{2} are tumor tissue specific heat capacity
and normal tissue specific heat capacity respectively

(5)

The value Q in the input matrix B represents the spatial power deposition at each finite difference node. The output matrix C of the model is represented by the location of the sensor.

The value Q in the input matrix B represents the spatial power deposition at each finite difference node. The output matrix C of the model is represented by the location of the sensor.

Where A is a tri diagonal system matrix incorporating both conduction and perfusion terms and B is the input matrix. For 1-D case the state T is a vector of temperatures elevation in the nodes of the tissue model and U is I(0) a single manipulated variable. The position of the ultrasound transducers is fixed and the magnitude of the ultrasound power is the only manipulated variable.

*Experimental Prototype*

An experimental set up similar to that used by Arora et.al
[13] was used for model validation and control experiments
and is shown in **Figure-2**. An 1-D cylindrical agar
phantom of length 13 cm and diameter of 1.27 cm was
considered. Condensed milk was added to mimic the ultrasound
absorption properties of human tissue [14]. Ultrasound
field was generated by single focused ultrasound
transducer resonating at a frequency of 2 MHz. The radius
of curvature and diameter of the transducer are 25cm and
7cm respectively. The agar phantom and the ultrasound
transducer are immersed in a bath of degassed water to
simulate the cooling effect of blood and to avoid the disturbance
caused by air bubbles. The RF signal generated
by a RF signal source and RF amplifier were used to drive
the transducer.

The temperature in the agar phantom was measured by a manganin-constantan thermocouple fixed on it. These thermocouples give an accuracy of ± 0.2 °C in temperature measurement over the range of 35°C -55°C, thereby eliminating the errors caused by conduction. Signal conditioning circuits and A/D cards are used to acquire and monitor the temperature.

## Methods

*Control Objective and Constraints*

For modeling and simulation purpose the desired temperature
was fixed to 43°C within the tumor while limiting
the temperature outside the tumor to safe levels of
less than 40°C .The objective of the control algorithm is
to track the step variations of the power input without
overshoot, with a rise time varying between 6 min and 12
min (6 min < t_{r} < 12 min) and to have a maximum settling
time of 12 min. In addition to the above the constraint on
the control signal is limited to Umax. Usually the maximum
allowed power deposition is determined by hardware
constraints or to avoid cavitations in tissues [2].

*Periodic Output Feedback Control Technique*

In periodic output feedback technique the input is changed several times in one output sampling instant .The poles of a controllable and observable system discretized at output sampling rate can be arbitrarily assigned by a piecewise constant periodic output feedback provided the number of gain changes during one output sampling interval [15,16,17].

The system after sampling by Γ secs

(6)

Assume (Φ_{Γ}
,C) F is observable and (F ,G) G controllable
with controllability indexg . Now the output sampling
interval is divided into N subintervals of length Δ=Γ/N
such that N ³ g . Thus the control law for POF controller is
given as

(7)

The sequence of N gains generate a time varying piecewise constant output feedback gains K(t) for 0 ≤ t ≤t .Sampling the simulated system by the sampling interval Δ, the delta sampled system is represented a

(8)

Define

(9)

A stabilizing output injection gain G_{0} is designed such that
the Eigen values of lie inside the unit circle.
The periodic output gain K is calculated solving

**ΓK**=G_{0} (10)

Where

The closed loop dynamic of the system with POF gain can be given as

(11)

The POF controller obtained by this method requires only
constant gains and hence easy to implement. A controller
designed as above will give desired closed loop behavior,
but strong oscillations exists between sampling instants
.Werner proposed a performance index such that *ΓK* » Γ_{0}
and ΓK=G_{0} need not be imposed [18]. This constraint is
replaced by a penalty function, which makes it possible to
enhance the closed loop performance, by permitting slight
variation from the original design and at the same time
improving the inter sample behavior. A tradeoff between
the closed loop performance and the similarity to the chosen
design is expressed by the quadratic performance index
as stated below is minimized

(12)

The state and input of the system are characterized as x_{l},
u_{l}, respectively. represents the state that would be
reached at the instant *k=lN*, given if k is solved to
satisfy GK = G exactly. Q, R and P are positive definite
symmetric matrices of appropriate dimensions. The first
term represents the state and the control energy of the
system and second term represents the penalty for the
deviation of the output injection gain from exact value
‘Go’. The POF gain calculated thus have very low magnitude
and is represented by K_{1} [19].

*Desired Trajectory*

A function which gives the desired trajectory for temperature evaluation at each point in tumor and in normal healthy tissues is framed from the control objective of the treatment protocol. For each perfusion case the performance analysis is done by calculating the error norm. The error norm is calculated as the 2-norm of the difference between the desired trajectory and the achieved output trajectories.

(12)

y des – Desired trajectory. yout- achieved output trajectory; e(t)- Error between the two temperature response.

## Result and Discussions

**System Simulation & Model Validation**

Temperature predictions from the simulated model are
validated with the measured temperature from the temperature
measured by the manganin-constantan thermocouple
and is shown in **Figure -3**. A step increase in ultrasound
power of 7 watts was applied prior to the treatment
session. To validate the simulated model with experimental
reading the temperature is measured at a single spatial
location at a distance of 2cm from the edge of the phantom
by fixing a thermocouple. Total of 200 temperature
data samples are recorded with the sampling time of 5
secs. The time temperature response at 20^{th} node from the
simulated mathematical model is also drawn and both
were compared. **Figure 3** shows the comparison between
the experimental output and simulated output. This shows
an accurate steady state prediction and there is a small
error in the time constant of the response. The reason for
this error is the Bio-heat transfer equation used for simulating
the model is 1-D where as the agar phantom used is
of diameter 1.25, the heat conduction in lateral direction
would have contributed for the plant model mismatch
created the error.

*POF controller design for varying blood perfusion*

Space discretization of the model gives rise to 131 nodes
including the boundary nodes. During hyperthermia blood
perfusion is the major variable that leads to parameter
variation. Perfusion conditions applied in simulation are
given as tumor perfusion W_{T} and normal tissue perfusion
W_{N}. The typical values W_{T} and WN used in hyperthermia
system modeling ranges from a lower extreme of 0.5
kg/m^{3}sec to a higher extreme of 10 kg/m^{3}sec[20] . Four
cases are considered with different combinations of WT
and W_{N} in this range, also simulations are also carried out
by varying thermocouple locations. The open loop time
temperature response is obtained by heating the tissue
tumor model with constant applied power for 60min.
Since it is a temperature process ‘τ 'is chosen to be
12secs. The original system is of 131 x131 orders. Since the system is too large for controller design the output
feedback controller design for the original system is done
via a reduced model of order 4. The number of gain
changes in one sampling interval is fixed as N = 4. So
Δ = Γ / N = 3sec s .

*Temperature response for normal tissue location and
tumor tissue location*

The response of the system in case-1 is shown in **Figure 4**,
The open loop step response, the closed loop response with
output injection gain G_{0}, the desired trajectory that meets the
primary goal of hyperthermia are shown in **Figure-4(a)**.The
closed loop performance of POF controller after optimization
procedure is in **Figure-4(b)** and the magnitude of the
control effort needed to achieve this response is in **Figure
4(c)**.The system dynamics without controller is not satisfactory
and it does not meet the requirements of hyperthermia
cancer treatments. The rate of temperature rise is very fast
and this may lead to patient discomfort and pain stimulation.
The prolonged settling time may cause hot spots and
cold spots inside the tumor leading to decrease in treatment
efficiency .This necessitates the need for a controller
.The closed loop response with POF controller closely
fallow the desired trajectory This will reduce the error
norms of the closed loop system. The closed loop response
with POF controller satisfies the requirements of
standard hyperthermia. Although the simulations are done for 60mins the time axis is limited to 1000secs to show
the effectiveness of the controller. Simulations are done
for cases 2, 3 and 4 also but response is shown only for
case-1.

**Figure 4:** *Temperature response for the perfusion case-i
(WT=0.5 kg/(m ^{3}sec) and WN =0.5 kg/(m^{3}sec). with Thermocouple
at normal tissue location (a) open loop and closed
loop response with state feedback and desired trajectory (b)
Closed loop response with Periodic Output Feedback Controller
and desired trajectory (c) Control input as a function
of time*

The control structure can be varied by changing the thermocouple
location. Now the thermocouple location is
changed to X=50 i.e. in tumor tissue. According to the
goals of hyperthermia temperature with in tumor tissue
should be ≥43°C. **Figure-5** shows the response for case-I
with thermocouple location at X=50.

**Figure 5:** *Temperature response for the perfusion case-i
(WT=0.5 kg/(m ^{3}sec) and WN =0.5 kg/(m^{3}sec). with Thermocouple
at tumor tissue location (a) openloop and closedloop
response with state feedback and desired trajectory
(b) Closed loop response with Periodic Output Feedback
Controller and desired trajectory (c) Control input
as a function of time*

**Table 2** shows that the inclusion of piecewise constant
periodic output feedback controller makes the system
closed loop stable and also the norm of the error between
the desired and the achieved trajectories for the open loop
and the closed loop system. The shapes of the achieved
trajectories show maximum consistency and the calculated
error norms do not show significant deviation. The
closed loop error norm is much less than the open loop
error norm indicating the performance of the designed
controller. Since the power deposition is more in the tumor
region variation in tumor perfusion W_{T} leads to a
larger effect on the temperature field. To overcome the
slow dynamics of the system higher control efforts are
needed at the beginning. For a given power input decrease
in blood perfusion causes an increase in system temperature.
**Table 3** shows the norm of error between the desired
and achieved trajectories for varying blood perfusion in
tumor tissue.

## Conclusion

Model validation results prove that the simulated model is a good approximation to the experimental prototype. Closed loop norms demonstrate the effectiveness of controller in achieving the goals of hyperthermia. It is found that the stabilizing controller designed from the reduced order model and applied to the higher order system performance and stability is guaranteed. Periodic output feedback controller developed is flexible and can be applied to hyperthermia models with changing blood perfusion leading to plant model mismatch. The suppression of fluctuations avoids hot spots and cold spots in tumor and surrounding tissues. The control effort is reduced by quadratic performance index optimization this avoids the controller saturation. For smaller perfusion rates the system settling time is longer. As the blood perfusion increases, it takes more heat away from the tissues and more control effort is needed to maintain a steady temperature. The output feedback controller effectively adjusts the power level of the ultrasound transducer according to the blood perfusion and other dynamic tissue properties to achieve controlled effective ultrasound hyperthermia. The results demonstrate that the periodic output feedback controllers are able to effectively track the target temperature with dynamic tissue properties. Achieving the desired trajectory leads to treatment precribability and this gives clinical acceptance to hyperthermia.

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