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1. Introduction {#sec1-materials-11-00019} =============== One focus of telemedicine is to provide health care in out-of-hospital settings. To that end, long-term remote patient monitoring, i.e., recording of vital signs like respiratory rate, electrocardiogram (ECG) or electrodermal activity (EDA), and interactive services for patient care have become available in recent years. Such developments can improve the quality of a patient's treatment by providing immediate access to healthcare. In particular, areas with high patient-to-doctor distance can benefit from such concepts \[[@B1-materials-11-00019]\]. However, even medically well-supplied areas can benefit, because long-term monitoring adds valuable information, whe compared to intermittent physical examinations by medical doctors. Besides, health care expenses can be reduced by gaining vital parameters remotely, without consulting a doctor \[[@B2-materials-11-00019]\]. The recording of biopotentials, i.e., electrical signals, is one essential aspect of remote monitoring systems \[[@B3-materials-11-00019],[@B4-materials-11-00019]\]. To monitor biopotentials in telemedical settings, skin electrodes are used. Typically, skin electrodes can be roughly classified into wet and dry electrodes \[[@B5-materials-11-00019]\]. The conventional Ag/AgCl wet electrodes are widely used in the clinical environment for measuring biopotentials, and possess the benefits of simplicity, low cost, and reliability. However, they have some limitations. The conductive gel dries over time, and is vulnerable to perspiration \[[@B6-materials-11-00019]\]. This hampers their application in long-term recordings because of their decreasing signal quality over time. Moreover, cleaning and skin preparation, which are necessary in order to yield the best possible conduction, can be time-consuming, particularly when using multiple electrodes. Finally, allergic dermatitis has been reported when using gel electrodes \[[@B7-materials-11-00019]\]. Dry electrodes have been developed to derive biopotentials without any need for skin preparation and conductive gel by using a benign metal. Although some patients developed a metal allergy \[[@B8-materials-11-00019],[@B9-materials-11-00019]\], dry electrodes can generally be assumed to improve patient comfort and ensure long-term applicability. However, such electrodes have the disadvantages of higher electrode-to-skin impedance, and are sensitive to movement artifacts \[[@B4-materials-11-00019],[@B6-materials-11-00019]\]. Furthermore, metal electrodes in combination with perspiration may degrade or lead to incompatibilities due to galvanic processes that generate unexpected ions \[[@B8-materials-11-00019]\]. Various designs have been developed to yield similar (electrical) properties to wet electrodes. Novel designs for measuring ECG or electroencephalogram (EEG) signals include needle electrodes \[[@B10-materials-11-00019]\], dry polymer electrodes \[[@B11-materials-11-00019],[@B12-materials-11-00019]\], so-called "epidermal electrodes" \[[@B13-materials-11-00019]\], and even textile-based dry electrodes \[[@B14-materials-11-00019],[@B15-materials-11-00019]\]. The latter are an essential component in the emerging field of adaptable, skin-mounted and wearable electronics \[[@B3-materials-11-00019],[@B16-materials-11-00019]\]. The challenge in the development of wearable skin electrodes is to fabricate lightweight, non-interfering, easy-to-handle, biocompatible, flexible electrodes that are capable of delivering good signal quality \[[@B5-materials-11-00019],[@B17-materials-11-00019]\]. This paper pursues an alternative approach for future healthcare applications: an on-demand electrode-skin contact module. As shown in [Figure 1](#materials-11-00019-f001){ref-type="fig"}, this comprises a polymeric substrate, electrodes, and an insulation layer, which typically separates the electrodes from skin contact. In case of measurement, the expandable pressure chamber establishes electrode-skin contact by inflating the chambers. After measurement or between measurement intervals, the pressure can be released or the chamber can be evacuated, retracting the electrode from the skin. This approach possesses three advantages: Firstly, the electrode being