1. Introduction
Mud is a blend of organic and inorganic substances dissolved in water that has experienced different geological and biological processes in a natural (or artificial) physiochemical environment [
1]. Natural thermal muds are traditionally used in therapeutic procedures. However, presently, cosmetics are typically processed (ground and mixed with other substances such as peat or clay). The processed thermal muds are used for therapeutic purposes under the name of peloids [
2].
Peloids are aimed at alleviating different ailments in traditional medicine and for application onto the skin in cosmetology, called pelotherapy under the general term balneotherapy [
2,
3]. Balneology is a research field of baths and bathing in natural waters for healing purposes, including the application of the emerging gasses and peloids [
4]. A method of pelotherapy is mud pack compress application—an option treating localized areas of the body to increase skin permeability and microcirculation [
5] or reducing pain in the case of knee osteoarthritis [
6]. The popularity of balneotherapy is increasing [
7], related to the perpetually-appearing new evidence of the advantageous effects of peloids on the human body [
8] and awareness of personal health. The utilization of peloids in natural cosmetics is also a rising trend, appearing in the wellness and relaxation field of medical and cosmetological applications [
9].
It is generally accepted that the skin, which is a very complex structure, is affected by a set of different factors of pelotherapy. Based on scientific evidence, the pelotherapeutic procedures are proposed, e.g., to relieve the joint pain of osteoarthritis of the knees [
10], to have a positive effect on gynecological problems [
11], to entail the passage of minerals through psoriatic skin [
12], and to enhance the superficial blood circulation [
5]. Pelotherapy has a useful effect on muscle tone and reduces pain through increasing temperature and hydrostatic pressure [
13].
The effect of pelotherapy can be evaluated directly or indirectly, from which the latter includes questionnaires and visual examination. The direct methods can be divided based on the utilized techniques, for example optical (laser Doppler flowmetry) [
5]; electrical (corneometry—for estimating the relative permittivity of the skin [
14]; electrical bioimpedance (EBI)); and blood analysis. A comprehensive overview of skin assessment techniques is given elsewhere [
15].
The primary front for peloids in balneotherapy is the skin—the largest organ in the human body, which is connected to the nervous system. Roughly, the stimulation of the skin by hot mud during pelotherapy is transferred through the sympathetic nervous system to the organs, which take part in metabolic processes of the human body [
3].
The human skin is a layered structure of different cell types, which perform various functions. Typically, the three layers of the skin are denominated: epidermis, dermis, and hypodermis. The epidermis can be divided into sublayers, starting with the outermost layer: stratum corneum (SC), stratum granulosum, stratum spinosum, and stratum basale [
16]. The SC at the forearm is about 10–20 µm thick and composed of stratified layers of dead and flattened cells, i.e., corneocytes [
17,
18]. The SC can be depicted as a brick wall, consisting of corneocytes’ extracellular matrix [
19]. The impedance of the SC depends on the moisture level in the air and sweating and can be considered as a dielectric in dry conditions [
20]. The remaining layers of the epidermis consist of nucleated cells and are typically 50–100 µm thick [
21].
The dermis of the forearm is roughly 1 mm thick and consists of elastic fibers, matrices of structural proteins, and cellulose—providing elasticity and strength to the skin. Together with the epidermis, the thickness has been reported to be 1.16–1.22 mm [
22]. The electrical conductivity of the dermis is reported to be higher than for the epidermis [
23]. The hypodermis is the bottom layer of the skin, consisting mainly of body fat together with blood vessels and nerves. The conductivity of the hypodermis has been reported to be low, however higher than that of the epidermis [
23].
It has been found by Martinsen et al. [
24] that, at low frequencies (below 1 kHz), the measured impedance of the skin is dominated by the SC. At higher frequencies (above 100 kHz), the viable skin dominates. Furthermore, the same authors showed that, at frequencies beyond 1 MHz, the contribution of the SC becomes very low, about 5% [
24].
EBI measurements have been successfully utilized in cardiac pacemakers: the impedance of the cardiac muscle is monitored to evaluate the energy balance to automatically set the rhythm [
25]. Furthermore, the dynamic change monitoring in the human body, caused by respiratory and cardiac activity, has been implemented—for example, to estimate the central aortic pressure of the blood [
26]. However, the EBI analysis of the skin has been implemented with various goals—e.g., to monitor skin cancer [
27], wound healing [
28], and the effectivity and the result of transdermal drug delivery [
29,
30].
The effect of curative mud on the human body has previously been researched by several studies on large groups of volunteers. Using laser Doppler flowmetry, the improvement in blood supply in the skin after the spa therapy procedures was confirmed statistically—more specifically, in the pelotherapy group [
31]. The same outcome was gained in a study including different blends of mud and peat, where the joint effect of both substances was determined: the moistening of the skin [
32].
The development of personalized medicine and the revolution in wellness towards sustainable and environmentally friendly technologies introduce the actuality of the object of our ongoing research. The elaboration of a precise and versatile methodology for assessing the effect of cosmeceutical substances on the skin constitutes a decent base for the further development of natural compounds in skin care products. Balneology, in general, and, more precisely, pelotherapy, with its complex palette of compounds, the complex effect of which on the human skin is assumed to provide surprising results, is already gaining popularity. The importance of the development and improvement of the means for detecting and discovering its effect is evident.
In this paper, we present the results of a pilot study to assess the effect of pelotherapy on the human skin (and underlying tissues) by using EBI analysis. Such research, including the specific effect of mud therapy, comprising the ability and different mechanisms of different substances to penetrate the skin barrier, by means of EBI has not been reported before. We introduced a measurement methodology by using local area mud pack application and custom-designed small-area electrodes on rigid printed circuit boards for monitoring the EBI of the skin. We demonstrate our findings by the determination of the effect of mud in comparison with the effect of tap water and the dry status of the skin in the case of measurements on both forearms. The clear difference between the mud-pack-treated and tap-water-treated skin appeared in the real part of the impedance in the frequency interval of 10 kHz …1 MHz, comprising the contribution of the current research.
The main purpose of the performed experiments was to create a methodology and increase the knowledge of the advantageous effect of pelotherapy to promote the application of mud therapy. This research project was ultimately expected to establish novel solutions and instrumentation that alter balneotherapy procedures to the current smart wellness and medical Internet-of-Things-based automatic supervision. The outcome was expected to provide prompt feedback on the effect of the performed pelotherapy to doctors and patients.
3. Materials and Methods
In this section, the requirements and the data of the volunteers are presented together with statistical analysis. The used materials (including the mud) with the description of the performed measurement procedures of EBI are described. Ultimately, the implemented method and developed EBI measurement electrodes are disclosed with insight into the model-based approach of representing the biological materials.
3.1. Choice and Data of Subjects
All the volunteers were introduced to the prepared information and agreement form and signed it thereupon. Secondly, a short health questionnaire was filled out by all the volunteers, requesting basic information concerning their health. After the review of the filled questionnaires by the doctors, ten healthy volunteers were chosen based on the following attributes:
Based on the filled forms, the data of the subjects were gathered, and the Body Mass Index (BMI) was calculated (the calculated mean values and standard deviations (
) for the whole sample size can be seen in
Table 1).
All of the volunteers were Caucasian and belonged to the interval of 20–40 years of age.
3.2. Materials
In this research, the focus was set on the determination of the effect of curative mud on human skin by electrical means. A mixture of wet unheated disintegrated mud of Haapsalu and peat was utilized. Based on the study of Estonian curative mud deposits by Terasmaa et al. [
54], the mud of Tagalahe Bay in Haapsalu is largely minerals, containing on average 11.7% of organic material.
For the experiments, a bag of synthetic fabric (5 × 10 cm) was filled with a mixture of mud and peat (1 tablespoon) (mud compress). The synthetic fabric enabled a small amount of mixture to remain outside and cover the skin surface. To exclude the placebo effect and compare it with the impact of some other wet substance, a piece of the same fabric, wetted with tap water at room temperature, was applied on the other forearm simultaneously (water compress).
The compress together with the arm was covered by thin polyvinyl chloride (PVC) film to avoid mud and water drying during the application.
In the current research, tape stripping was not used to disrupt the skin barrier and ease the passage of substances. This decision was based on the fact that such a practice is not common in pelotherapy and mud pack therapy. Instead, our goal was to imitate the actual conditions of the targeted procedure.
3.3. Measurement Procedure
Four measurement cycles were performed in the cases of each volunteer:
EBI measurement of the skin on the left forearm (A);
EBI measurement of the skin on the right forearm (B);
Application of the mud compress on the left forearm and the subsequent EBI measurement of the skin (C);
Application of the water compress on the left forearm and the subsequent EBI measurement of the skin (D).
The choice of the forearms was intentional because the correlation between the BMI and the skin thickness in this body area has been reported to be the lowest [
22]. Furthermore, the thickness of the SC at the ventral side of the forearm is reported to be one of the lowest in the human body [
55], while diverging in the left and right forearm on average 0.03 mm [
22]. There is a difference in the thickness of the skin based on sex. The average skin thickness of men on the ventral side of the forearm is 1.26 mm and, for women, 1.12 mm.
The procedure in the cases of Measurement Cycles A-B is described step-by-step in the following listing:
The volunteer was sitting on the chair with the hand lying on the armrest at the height of about the last rib in the case of a horizontally bent arm (with the inner side of the forearm slightly exposed upwards);
The area under the electrode on the surface of the skin was slightly moistened with a wet paper towel;
The electrode was placed on about the area of the centerline of the middle side of the forearm and fixed by using a gentle medical tape (
Figure 1);
EBI measurement was performed 3 min after the electrode was attached to the skin surface;
The tape with the electrode was removed.
The procedure in the cases of Measurement Cycles C-D is described step-by-step in the following listing:
The compress of mud (Cycle C) (
Figure 2a) or water (Cycle D) (
Figure 2b) was placed on the inner side of the forearm and covered with PVC film.
The PVC film and compress were removed after 30 min.
Step 1 in the case of Measurement Cycles A-B.
Loose water and mud were removed from the surface of the skin by using a paper towel.
Step 3 in the case of Measurement Cycles A-B.
Step 4 in the case of Measurement Cycles A-B.
Step 5 in the case of Measurement Cycles A-B.
Three repetitive measurements were performed in each cycle.
3.4. Measurement Method
The impedance measurements were performed by using the four-electrode measurement system. The choice was made to avoid the electrode polarization impedances of current-carrying (CC) electrodes (applied in the case of two-electrode systems). An important aspect to consider hereby is the depiction of an object (in the current paper, the human skin) by its measured electrical behavior. In the case of a four-electrode system, the trans-impedance is a more precise term to use than impedance. In the case of a four-electrode system, two two-electrode systems are present—one for excitation and one for measurement [
20].
Thus, the geometrical aspect must be considered due to the expected formulation of sensitivity fields in an object because of the possible interposition of voltage and current lead fields. Therefore, besides the zero sensitivity, positive and negative sensitivities may appear, affecting the total measured impedance [
20].
The electrodes play a substantial role in the electrical measurement of biological objects, explained by the different types of current carriers when compared to solid matter. A comprehensive definition is provided in [
20]: the electrode is the site of a shift from electronic to ionic conduction and vice versa. What happens is the exposure of layers of different materials, which, in the case of low-frequency measurements, gives birth to interfacial polarization [
56]. This is caused by charge accumulation at the interface of the electrode and object (SC at non-invasive measurements) in the presence of the external electric field.
Moreover, in the case of non-invasive measurements, the electric connection strongly depends on the status of the object’s surface—the skin. These measurements incorporate time-dependent factors such as hydration, sweating activity, and emotional state [
50]. However, the measured data must be gathered simultaneously, i.e., the signals must be processed and evaluated in correlation with the physical and emotional state of the subject and the surrounding environment.
In the case of electrolytes (i.e., wet SC at non-invasive measurements), the emergence of an electrical double-layer must be considered. The double-layer is caused by the contact of materials of different molecular structures where only the electrolytic side contributes (as the electrodes in metal are strictly bound) [
20]. The electrical double-layer exhibits capacitive properties that are in series with the electrode; however, it is never a pure parallel-plate capacitor, as this layer is leaky and potential- and concentration-dependent [
56].
The electrode material is a relevant issue as the polarization phenomenon is related to this choice. The non-polarizable electrodes are expected to achieve resistive contact with the object, while in the case of polarizable electrodes, the contact is expected to be capacitive. However, in practice, the electrodes are somewhat polarizable and somewhat non-polarizable, i.e., experiencing a finite faradaic impedance [
57].
Other important aspects are the shape, dimensions, and distances between the electrodes when measuring the impedance of human skin. It has been reported that, in the case of a two-electrode system, the distance between the electrodes influences the measuring depth. Specifically, the penetration depth of currents in the object is half of the distance between the electrodes [
20,
27]. However, as discussed before, in the case of a four-electrode system, the contribution of different layers in the object is more complicated because of the geometrical aspect. On the other hand, the electrode area can be expected to influence the sensitivity in the gap between the electrodes; the narrower the gap, the higher the sensitivity is [
20].
The importance of the choice of the shape and dimensions of the electrodes appears when measuring the human skin—related to its relatively small thickness and the presence of the sweat ducts. The gap between the electrodes cannot be smaller than the diameter of sweat duct (approximately 20 µm); otherwise, the small-sized electrodes could face a shunt path due to the relatively well-conducting sweat. This can be taken as a minimum gap; however, the conductivity of the SC is variable, and sweating SC can shunt the electrodes in applicable conditions.
Standard pre-gelled Ag/AgCl electrodes are very useful due to their standard design; however, problems appear. The electrode gel affects the SC through several mechanisms (for a comprehensive overview, see [
46]). Importantly, the electrode gel may depend on the type or decrease or increase the electric parameters of the SC and influence the measured Y [
20,
46]. No less important, as expected in [
20], the substances from the electrode gel may penetrate the SC, influencing the measured electrical characteristics of the skin [
50].
Another possible way to approach the skin is to use interdigitated electrodes [
58], which could be used to attain the mean of the underlying area on the skin. Another option is to use the quasi-monopolar configuration, which is reported to provide the feature of targeting the sensitivity of the skin area of interest [
59].
For the current research, the choice was made to design gold-plated electrode contact surfaces on rigid FR-4 material (with a thickness of 1.6 mm) as a printed circuit board (PCB). The electrodes were manufactured by a standard rigid PCB manufacturing process: etching (1), photoengraving (2), and laminating (3) (no more additional steps were need as it was a simple two-sided PCB with no holes). On the top side of the PCB, copper fields for surface-mountable connectors were formed (
Figure 3b). The copper fields on the electrode side (bottom) were galvanically gold-plated. The design is explained by the desire to ease the connection of the impedance spectroscope to the electrodes. The rigid electrodes provide the advantage of maintaining the fixed gap between the electrode contact surfaces and the possibility of attaching the designed PCB to the skin’s surface by using sticky tape. For the planned pilot study, the application of a miniature simplistic design of electrodes is valid as the effect of pelotherapy can be expected to apply equally on the skin surface.
The gap between the electrodes was 2 mm and the width of the electrode contact surface 1 mm (for the dimensions, refer to
Figure 3a). The choice is explained by the wish to concentrate on a small skin area with the presumption of its relative uniformity. The electrode contact surfaces were galvanically gold-plated. The choice of gold plating originated from the expectation that the capacitive properties of the SC dominate in the dry condition of the skin [
57]. As a result, the polarization properties of gold are hidden by the capacitive properties of the SC, which are of a much larger scale. However, with the increase of moisture in the SC and sweating, its capacitive properties disappear quickly and are replaced by resistive ones. However, gold is durable and has constant properties when compared to medical-grade gel electrodes, which are inconvenient in application.
3.5. Used Devices
For measuring EBI, a laboratory on-desk impedance spectroscope HF2IS together with an HF2TA transimpedance amplifier from Zurich Instruments was used. This device proposes the frequency range of 0.7 μHz–50 MHz and the possibility of using two- and four-electrode measurements [
60].
The question of the excitation signal was solved by using a wide frequency sweep in the range of 100 Hz–20 MHz with an amplitude of 500 mV. However, during the data analysis, the suitable frequency intervals were sorted.
The question, accompanying the planning of electrical measurements of biological objects, is the choice of the parameters that would incorporate the data of interest. In the case of variable biological processes—such as the flow of pulsating blood in arteries—the ratio of change in the volume can be calculated and compared in situ while rejecting the uncertainties this originates from the interface between the skin and electrode [
61]. However, when the focus is to measure the absolute value of
Z, the object’s (i.e., the skin) properties must be considered thoroughly. For this reason, the real and imaginary parts of both—
Z and
Y—were gathered, compared, and evaluated.
As Z is a complex term (so is Y), consisting of the real and imaginary parts, originating from the layers of matter of better and worse conductivity, the consideration is the model-based representation of the skin.
3.6. Skin Impedance Models, i.e., the Method
The interfacial polarization problem can be addressed when depicting the structural composition of the skin. Biological objects can be represented by an equivalent circuit that consists of series and parallel combinations of resistors (
R) and capacitors (
C). These circuits behave very differently under the excitation of different frequencies. In the case of a series combination of RC circuits, the result is the summation of both elements. In the case of a parallel connection, the frequency dependence appears; at the low frequencies, the
Z is contributed by resistors, while at the high frequencies, by capacitors [
20].
Based on the above description, the electrical model of complex biological tissue (and skin) cannot be presented just by using series and parallel RC circuits. To add the frequency dependence, the inclusion of a constant phase element (CPE) is typically performed. The CPE depicts a non-ideal capacitor that is used instead of an ideal capacitor ( = 1) in the circuit together with a resistor ( = 0).
The impedance of the CPE (
) can be rewritten as
The dependence of the impedance of an object to the frequency is described by Cole’s equation:
ZCPE is an empirical function, used in fitting the measured impedance of a biological object [
62]. The parameter
denotes the displacement of the center of the circular arc below the real axis in the impedance phasor diagram. The Cole model is popular for characterizing the impedance data of biological objects because of its mathematical plainness and simple empirical equivalent circuit. Still, the utilization of RC layered models has been presented in the literature as well [
58,
63]—being in some cases complicated combinations of parallel and series RC circuits with more than 20 parameters [
62].
In combining these two models, the most accurate one is expected to be achieved by adopting the
ZCPE element in each layer’s RC structure [
62]. However, we cannot describe the structure and dimensions of the skin layers of all subjects individually. However, generally, the structure can be described. A commonly accepted electrical model of the skin is a distillation of the previously noted model, consisting of the parallel connection of DC conductance and the polarization impedance of the system (both frequency0dependent) in series with resistance R∞, denoting the hypodermis [
39,
53,
64].
The equation of
Z being equal to the inverse of
Y is true only in the case of linear conditions (homogeneous tissue structure). However, it does not apply to the real and imaginary parts of
Z and
Y because of the frequency dependence of the complex layered and inhomogeneous structure of the skin [
20]. The data representation must be performed based on the chosen model.
Typically,
Z is used to describe the object when it is represented as layers of different conductivity (parallel connections of single resistors
R and single capacitors
C) in series (
Figure 4a), and
Y is used when the layers are in parallel (
Figure 4b) [
20].
In the case of the parallel connection of the layers, the calculation of
Y is straightforward: G1 + G2 and C1 + C2. In the case of the series model, the calculation gains a much more complex character because of the accompanying frequency dependence (at low frequencies, the current prefers to flow through the resistors and, at high frequencies, through the capacitors) [
20].
For measuring the impedance of the skin, the series model is typically used (because of the layered structure of the skin); however, when considering the equivalent skin model, one can realize that it is not so straightforward. It can be imagined that the skin consists of several parallel and series RC connections, and the behavior is a combination of the response of these connections. Ultimately, this means that the data of interest are not expected to be incorporated only into the measured Z (series connection), but also into the measured Y (parallel connection).
Based on this consideration, the decision was made to gather altogether 3 datasets in each measurement cycle:
Z and ;
R and X;
G and B.
However, Reference [
53] stated that, concerning skin hydration, all the necessary information can be found by implementing the low-frequency
B measurements at a single frequency. This is explained by the influence of sweat ducts, which provide direct pathways through the skin while expectedly containing a minor amount of information about the skin (when measuring
G). Still, the effect of curative mud on the skin is expected to be the result of a combination of different factors [
13,
34]. At the same time, this witnesses that the useful data may be contained by the resistive parts as well.
4. Measurement Results
The datasets from the impedance spectroscope were in the .csv format, while the processing and analysis were implemented in Microsoft Excel.
In the cases of the results of Cycles A and B, the dispersion was larger than in the cases of Measurement Cycles C and D. This was the result of uncertainties, caused by the interface between the dry electrode contact surfaces and the dry skin. The quality of the electrical connection in the described case depended on the level of sweating and the air humidity, i.e., dominated by the status of the SC. If the electrode is set on the skin for three minutes, the conditions equalize at some level; however, the dispersion of the results will still be larger than in the case of wetting the skin for 30 min with a wet compress (mud or water). The building up of water contact with the dry electrode may take 15 min or more [
20].
To analyze and represent the measurement data in this section, the mean of three repetitive measurements was used.
The research was carried out by following the principles embodied in the Declaration of Helsinki and local statutory requirements. The gathered data were subjected to anonymization in all cases by adding an identification number to the subject; the gathered data cannot be connected to specific individuals. The study was performed under the approval of the Tallinn Medical Research Ethics Committee (Estonia) (Decision No. 2542). No difference between the sexes of the volunteers in the results was focused on nor noticed.
4.1. Verification of the Measurement Setup
To verify the chosen setup for the impedance measurements of the skin, an experiment in the cases of circuits of passive discrete electronic components was performed. The measurement was performed in the range of 1 kHz–2 MHz, as expectedly, at the lower frequencies, Z will resemble R. The possibility of a discrepancy between the measured and calculated values of Z was expected to appear at higher frequencies, however well below 1 MHz.
Three equivalent circuits were composed to represent the
Z of the skin: a single resistor (100 Ω) (
Figure 5b, circuit A); series connection of the resistor (1 kΩ) and capacitor (22 nF) (
Figure 5b, circuit B); parallel connection of the resistor (1 kΩ) and capacitor (22 nF) (
Figure 5b, circuit C). General through-hole 0.5 W metal film resistors and ceramic capacitors were utilized and soldered to the breadboard PCB.
Resistors with a value of 10 kΩ represent the resistances of the current-carrying electrodes, while the resistances of the measuring electrodes were considered negligible.
The impedance spectroscope HF2IS together with the HF2TA transimpedance amplifier (Zurich Instruments AG, Zurich, Switzerland) was used to measure the impedance of the composed equivalent circuits with similar parameters as the properties of the skin in the following sections.
The results (measured and calculated curves) in the cases of all three verification circuits are visible in
Figure 5a, where
Z and
F are shown in a logarithmic scale.
Z was calculated according to the equation:
where
C is capacitance and
f is frequency. In the calculated
Z, the
R of the current-carrying electrodes was not included to imitate the ideal approach.
Starting at about a frequency of 200 kHz, a deviation of the measured value of Z from the calculated value of Z appeared. The increase in the value of the measured Z at higher frequencies was expected to appear because of the effective parasitic elements in the measurement setup—caused, e.g., by connecting wires of finite length and the input capacitance of the measurement device. Nevertheless, the agreement of the measured values of Z with the calculated values of Z was obvious in the chosen frequency interval, i.e., the chosen measurement setup is valid. However, at frequencies above 200 kHz, the contribution of the parasitic elements to the measured value of Z must be considered. Still, this effect can be expected to apply equally (theoretically) to all the measurements of Z, i.e., the results were comparable.
4.2. Immittance Measurements of the Skin
The results of the immittance measurements of the dry skin and the skin that was treated by mud and water compresses are represented in this section. To detect the possible effect of the mud on the skin, the measured Z and Y together with the real and imaginary parts are presented individually.
Reference [
20] states that focusing on the real and imaginary parts of immittance when evaluating skin status is justified in certain cases. This applies, e.g., in monitoring the hydration of the skin, where the relevant data are claimed to lie in the measured low-frequency
B [
53]. When applying a wet compress, the skin is hydrated, i.e., a similarity can be recognized. In the current research, dry gold-plated electrodes were used, and the polarization impedance was expected to affect the measured immittance at low frequencies.
4.2.1. The Magnitude and Phase Angle of the Measured Impedance of Skin
The calculated means of the measured
Z and
of the skin before and after the application of both compresses can be seen in
Figure 6 and
Figure 7.
Based on the evaluation of the measurement results, a distinguishable response pattern of (but, also Z), falling into recognizable intervals in the frequency domain, can be noticed. This is explained by the mechanisms (properties of the skin) that apply at different excitation signal frequencies (dispersions). Based on that phenomenon, the utilized frequency range in the current paper was divided into three frequency intervals and followed accordingly in the following sections:
100 Hz …10 kHz;
10 kHz …1 MHz;
1 MHz …20 MHz.
To illustrate the distribution of individual measurement results,
Figure 8 can be evaluated, where the values of
are plotted.
Figure 8 shows the
in the case of
Z measurement before the application of the mud/water compress. As in this case, presumably, the measured values of
Z were the highest, these indicated the distribution of the measurement results of 10 volunteers the best.
To identify the effect of mud and water compresses on dry skin, simultaneously, correlation coefficients (
r) were calculated for the three cases among the three proposed frequency intervals: before the mud/water compress to after the mud compress (BMWC-AMC), before the mud/water compress to after the mud compress (BMWC-AWC), and after the mud compress to after the water compress (AWC-AWC), denoted as
and
,
and
, and
and
. The results can be seen in
Table 2.
The correlation coefficients indicate an important pair of properties of the linear relationship between two variables (data sets): strength (1) and direction (2). Depending on the amount of sample data (which, in the context of the current manuscript, is reasonable—10 volunteers), conclusions can be drawn, especially in the case of significant differences in the calculated statistical data.
4.2.2. The Conductance and Susceptance of the Measured Admittance of Skin
The calculated means of the measured
G and
B of the skin before and after the application of mud and water compresses can be seen in
Figure 9a,b, respectively.
The complex plane representation gives an idea of the variation of
G and
B and is visible in
Figure 10.
The calculated correlation coefficients (
r) in the cases of
G and
B among the three proposed frequency intervals for the three skin conditions (BMWC-AMC, BMWC-AWC, and AWC-AWC), denoted as
and
,
and
, and
and
, can be seen in
Table 3.
4.2.3. The Resistance and Reactance of the Measured Impedance of Skin
As shown already in
Figure 4, the content of the measured data that are represented by
Z and
Y was expected to depend on the construction of an object under test. Generally, the skin (and more so also the SC [
19]) is reported to be a layered structure, which in electrical terms resembles a parallel connection of passive electronic components, so
R and
X are expected to incorporate additional information.
The calculated means of the measured
R and
X of the skin before and after the application of mud and water compresses can be seen in
Figure 11a,b respectively.
The representation of the calculated mean
R and
X in the complex plane revealed a noticeable difference between the statuses of the skin before and after the application of mud and water compresses, especially in the low- and medium-frequency interval (
Figure 12).
As the data in
Figure 12 in the case of the measurements before mud and water compress spread over a significantly wider dispersion of values, minimizing the results of the measurements after the mud and water compress visually,
Figure 13 is included. Based on
Figure 13, a comparison can be made for measurements after the mud and water compresses.
The calculated correlation coefficients (
r) in the cases of
R and
X among the three proposed frequency intervals for the three skin conditions (BMWC-AMC, BMWC-AWC, and AWC-AWC) denoted as
and
,
and
, and
and
can be seen in
Table 4.
6. Limitations of the Work
The authors realize that the defined attributes for hiring the volunteers into the study were expected to set limitations on the study and the extraction of the measurement results. However, the main reason for such attributes was to limit the group of subjects based on similar physiological characteristics to enhance the manifesting of a possible effect of pelotherapy. A wider sample size and range of chosen attributes will be a matter of thorough study in the next research phase.
Another major limitation of the current work is that all the volunteers were Caucasian. However, the next, exhaustive study will cover a wider group of volunteers.
Furthermore, one controversy is related to the conditions (environmental, physical, etc.) in which pelotherapy is performed. Mud baths are given traditionally in a specific environment (where a specific room and mud temperature and air humidity are applied), either in a spa or in dedicated locations in the natural environment. We performed the mud pack therapy in the laboratory environment, where there are no spa conditions. However, mud pack therapy is gaining more and more attention in rehabilitation today, applied also in home conditions, providing positive results.
7. Conclusions
In this paper, we provided evidence of the effect of pelotherapy on the human skin present in the measured data of EBI. We showed that the effect is likely to be observable in the real and imaginary parts of Z (R and X). The developed and presented approach of monitoring the effect of pelotherapy is novel together with the findings of the correlation between the measured values of the EBI of the skin before and after the applied treatment with the mud. Similar findings have, based on our best knowledge, never been published before.
The finding of the poor correlation between the measured values of R before the application of the mud/water compress (dry skin) and after the mud compress and the very strong correlation before the application of the mud/water compress (dry skin) and after the water compress is the highlight based on the performed research. This finding was confirmed by the similar (not equally deep, but still distinctive) discovery in the X domain. The frequency interval was a key aspect here: the finding appeared in the frequency interval of 10 kHz …1 MHz, which, based on our results, is suggested for mud pack therapy effect detection.
From the viewpoint of pelotherapy, this finding could open a new modality in monitoring the effect of the performed thermal mud procedure. Pelotherapy, which is a promising rehabilitation method (i.e., cardiac) could gain more scientific proof through standardized measurements—based on bioimpedance analysis. Ultimately, medical-grade devices could emerge, relying on the EBI measurements, to give input to the medical diagnostics to adjust the therapy or assess its effect.
The following assumptions can be made based on the mineral concentrations and skin electrical properties. During mud pack therapy, the salts dissolved into the skin, and throughout, the increased moisture caused the measured R to differ significantly from the measured R after tap water application in the selected frequency interval (10 kHz …1 MHz). However, the differences in X at the same second frequency interval refer to changes in the polarization of cellular membranes, proteins, and other organic macromolecules—possibly related to the specific effect of pelotherapy. However, the exact mechanism is complex and still debatable, as the differences in the imaginary parts of the immittance were revealed concurrently, while the separation of the specific and non-specific effects of pelotherapy needs further research.
Referring to the desire of realizing the body-measuring solution as a portable device, the suitable frequency interval, most affected by the effect of pelotherapy, was identified. Moreover, the possibility of using simple electrical measurements, already in use in pharmacology for detecting the amounts of delivered drugs through the skin, is expected to open a new modality in providing evidence of the effect of pelotherapy and eventually promoting spa procedures.
Further research on the effect of pelotherapy on the skin is planned to gain elaborate measurement results of EBI for comparison and analysis. The number of volunteers will be increased together with an expanded range of requirements. Attention will be turned to the choice of the electrode because of the indistinct effect of the utilized classical tetrapolar electrode configuration—implemented on a rigid PCB. The electrode will be highly flexible and contain hydrogel between the skin and electrode contact surfaces to achieve a good electrical connection to the skin.
As a future target, the recovery of the skin from the effect of pelotherapy will be added to the research plan—-implemented as a time-based measurement of EBI after the removal of the mud. The tape-stripping method will be considered to mechanically disrupt the skin barrier. Related to the interest in the ability of biologically active substances in the form of humin peloids to pass through the skin barrier and their positive effect on blood micro-circulation and the reduction of inflammation, the development of a suitable method will be decided.